Nad(p) depot for nad(p)-dependent enzyme-based sensors

ABSTRACT

The present disclosure provides analyte sensors including one or more NAD(P)-dependent enzymes and an internal supply of NAD(P) for the detection of an analyte. The present disclosure further provides methods of using such analyte sensors for detecting one or more analytes present in a biological sample of a subject, and methods of manufacturing said analyte sensors.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to U.S. Provisional Application No.63/125,846, filed Dec. 15, 2020, the contents of which is incorporatedby reference in its entirety.

FIELD

The subject matter described herein relates to analyte sensorscomprising an NAD(P) depot and methods of using the same.

BACKGROUND

The detection of various analytes within an individual can sometimes bevital for monitoring the condition of their health as deviations fromnormal analyte levels can be indicative of a physiological condition.For example, monitoring glucose levels can enable people suffering fromdiabetes to take appropriate corrective action including administrationof medicine or consumption of particular food or beverage products toavoid significant physiological harm. Other analytes can be desirable tomonitor for other physiological conditions. In certain instances, it canbe desirable to monitor more than one analyte to monitor single ormultiple physiological conditions, particularly if a person is sufferingfrom comorbid conditions that result in simultaneous dysregulation oftwo or more analytes in combination with one another.

Analyte monitoring in an individual can take place periodically orcontinuously over a period of time. Periodic analyte monitoring can takeplace by withdrawing a sample of bodily fluid, such as blood or urine,at set time intervals and analyzing ex vivo. Periodic, ex vivo analytemonitoring can be sufficient to determine the physiological condition ofmany individuals. However, ex vivo analyte monitoring can beinconvenient or painful in some instances. Moreover, there is no way torecover lost data if an analyte measurement is not obtained at anappropriate time.

Continuous analyte monitoring can be conducted using one or more sensorsthat remain at least partially implanted within a tissue of anindividual, such as dermally, subcutaneously or intravenously, so thatanalyses can be conducted in vivo. Implanted sensors can collect analytedata on-demand, at a set schedule, or continuously, depending on anindividual's particular health needs and/or previously measured analytelevels. Analyte monitoring with an in vivo implanted sensor can be amore desirable approach for individuals having severe analytedysregulation and/or rapidly fluctuating analyte levels, although it canalso be beneficial for other individuals as well. Since implantedanalyte sensors often remain within a tissue of an individual for anextended period of time, it can be highly desirable for such analytesensors to be made from stable materials exhibiting a high degree ofbiocompatibility.

However, implantable sensors can be plagued by short life spans orreduced sensitivity. For example, many implantable sensors use enzymesfor continuous monitoring of analyte levels in vivo and many of theseenzymes rely on coenzymes for activity. For example, nicotinamideadenine dinucleotide (NAD) and nicotinamide adenine dinucleotidephosphate (NADP) are two of the most important coenzymes found in livingcells, and are frequently required for the activity of enzymes such asdehydrogenases that are found in implantable sensors. The amount of NADor NADP available for use by the enzymes present in implantable sensorscan affect the sensitivity of the sensor to accurately monitor analytelevels in vivo. Under certain circumstances, exogenous NAD or NADP maynot be present in sufficient quantities to support sensor operation or,even if sufficient exogenous quantities exists, such molecules are toolarge to readily diffuse to the area of the sensor that retains theenzyme dependent on NAD or NADP, which can lead to reduced sensitivity.Accordingly, there is a need in the art for sensors that retainsensitivity over longer periods of time.

SUMMARY

The purpose and advantages of the disclosed subject matter will be setforth in and are apparent from the description that follows, as well aswill be learned by practice of the disclosed subject matter. Additionaladvantages of the disclosed subject matter will be realized and attainedby the devices particularly pointed out in the written description andclaims hereof, as well as from the appended drawings.

To achieve these and other advantages and in accordance with the purposeof the disclosed subject matter, as embodied and broadly described, thedisclosed subject matter provides analyte sensors that include aninternal supply of NAD(P). For example, and not by way of limitation, ananalyte sensor of the present disclosure includes an internal supply ofNAD(P), a permeable polymer that overcoats the internal supply ofNAD(P), at least a first working electrode that is disposed upon asurface of the permeable polymer, an analyte-responsive active areadisposed upon a surface of the first working electrode and, optionally,a mass transport limiting membrane permeable to the analyte thatovercoats at least the analyte-responsive area.

In certain embodiments, the analyte is selected from the groupconsisting of glucose, a ketone, an alcohol, lactate and a combinationthereof. In certain embodiments, the analyte is glucose. In certainembodiments, the analyte is a ketone. In certain embodiments, theanalyte is lactate. In certain embodiments, the analyte is an alcohol,e.g., ethanol.

In certain embodiments, the first working electrode is a permeableworking electrode. In certain embodiments, the permeable workingelectrode comprises a carbon nanotube.

In certain embodiments, the analyte-responsive active area comprises anNAD(P)-dependent enzyme. In certain embodiments, the NAD(P)-dependentenzyme is an NAD(P)-dependent dehydrogenase. In certain embodiments, theNAD(P)-dependent enzyme present within the analyte-responsive activearea is β-hydroxybutyrate dehydrogenase. In certain embodiments, theNAD(P)-dependent enzyme present within the analyte-responsive activearea is glucose dehydrogenase. In certain embodiments, theNAD(P)-dependent enzyme present within the analyte-responsive activearea is a lactate dehydrogenase. In certain embodiments, theNAD(P)-dependent enzyme present within the analyte-responsive activearea is an alcohol dehydrogenase. In certain embodiments, theNAD(P)-dependent enzyme present within the analyte-responsive activearea is diaphorase.

In certain embodiments, the permeable polymer comprises a poly(propyleneglycol)-based polymer. In certain embodiments, the permeably polymercomprises poly(propylene glycol) methacrylate and/or 2-hydroxyethylmethacrylate.

In certain embodiments, the analyte-responsive active area furtherincludes a diaphorase. In certain embodiments, the analyte-responsiveactive area further includes a redox mediator.

In certain embodiments, an analyte sensor of the present disclosurefurther includes a second working electrode and a second active areadisposed upon a surface of the second working electrode and responsiveto a second analyte differing from the first analyte. In certainembodiments, the second active area includes at least one enzymeresponsive to the second analyte. In certain embodiments, a secondportion of the mass transport limiting membrane overcoats the secondactive area.

The present disclosure further provides methods for monitoring ananalyte in vivo. In certain embodiments, the method can includeproviding an analyte sensor comprising (a) an internal supply of NAD(P),(b) a permeable polymer that overcoats the internal supply of NAD(P),(c) at least a first working electrode that is disposed upon a surfaceof the permeable polymer, wherein the first working electrode is apermeable working electrode, (d) an analyte-responsive active areadisposed upon a surface of the first working electrode, wherein theanalyte-responsive active area comprises an NAD(P)-dependent enzyme and(e) a mass transport limiting membrane permeable to the analyte thatovercoats at least the analyte-responsive area. In certain embodiments,the method further includes applying a potential to the first workingelectrode, obtaining a first signal at or above an oxidation-reductionpotential of the first active area, where the first signal isproportional to a concentration of a first analyte in a fluid contactingthe first active area, and correlating the first signal to theconcentration of the first analyte in the fluid.

In certain embodiments, the analyte sensor for use in the disclosedmethods can further include a second working electrode and a secondactive area disposed upon a surface of the second working electrode andresponsive to a second analyte differing from the first analyte. Incertain embodiments, the second active area includes at least one enzymeresponsive to the second analyte and a second portion of the masstransport limiting membrane overcoats the second active area.

BRIEF DESCRIPTION OF THE DRAWINGS

The following figures are included to illustrate certain aspects of thepresent disclosure and should not be viewed as exclusive embodiments.The subject matter disclosed is capable of considerable modifications,alterations, combinations, and equivalents in form and function, withoutdeparting from the scope of this disclosure.

FIG. 1A is a system overview of a sensor applicator, reader device,monitoring system, network and remote system.

FIG. 1B is a diagram illustrating an operating environment of an exampleanalyte monitoring system for use with the techniques described herein.

FIG. 2A is a block diagram depicting an example embodiment of a readerdevice.

FIG. 2B is a block diagram illustrating an example data receiving devicefor communicating with the sensor according to exemplary embodiments ofthe disclosed subject matter.

FIGS. 2C and 2D are block diagrams depicting example embodiments ofsensor control devices.

FIG. 2E is a block diagram illustrating an example analyte sensoraccording to exemplary embodiments of the disclosed subject matter.

FIG. 3A is a proximal perspective view depicting an example embodimentof a user preparing a tray for an assembly.

FIG. 3B is a side view depicting an example embodiment of a userpreparing an applicator device for an assembly.

FIG. 3C is a proximal perspective view depicting an example embodimentof a user inserting an applicator device into a tray during an assembly.

FIG. 3D is a proximal perspective view depicting an example embodimentof a user removing an applicator device from a tray during an assembly.

FIG. 3E is a proximal perspective view depicting an example embodimentof a patient applying a sensor using an applicator device.

FIG. 3F is a proximal perspective view depicting an example embodimentof a patient with an applied sensor and a used applicator device.

FIG. 4A is a side view depicting an example embodiment of an applicatordevice coupled with a cap.

FIG. 4B is a side perspective view depicting an example embodiment of anapplicator device and cap decoupled.

FIG. 4C is a perspective view depicting an example embodiment of adistal end of an applicator device and electronics housing.

FIG. 4D is a top perspective view of an exemplary applicator device inaccordance with the disclosed subject matter.

FIG. 4E is a bottom perspective view of the applicator device of FIG.4D.

FIG. 4F is an exploded view of the applicator device of FIG. 4D.

FIG. 4G is a side cutaway view of the applicator device of FIG. 4D.

FIG. 5 is a proximal perspective view depicting an example embodiment ofa tray with sterilization lid coupled.

FIG. 6A is a proximal perspective cutaway view depicting an exampleembodiment of a tray with sensor delivery components.

FIG. 6B is a proximal perspective view depicting sensor deliverycomponents.

FIGS. 7A and 7B are isometric exploded top and bottom views,respectively, of an exemplary sensor control device.

FIG. 8A-8C are assembly and cross-sectional views of an on-body deviceincluding an integrated connector for the sensor assembly.

FIGS. 9A and 9B are side and cross-sectional side views, respectively,of an example embodiment of the sensor applicator of FIG. 1A with thecap of FIG. 2C coupled thereto.

FIGS. 10A and 10B are isometric and side views, respectively, of anotherexample sensor control device.

FIGS. 11A-11C are progressive cross-sectional side views showingassembly of the sensor applicator with the sensor control device ofFIGS. 10A-10B.

FIGS. 12A-12C are progressive cross-sectional side views showingassembly and disassembly of an example embodiment of the sensorapplicator with the sensor control device of FIGS. 10A-10B.

FIGS. 13A-13F illustrate cross-sectional views depicting an exampleembodiment of an applicator during a stage of deployment.

FIG. 14 is a graph depicting an example of an in vitro sensitivity of ananalyte sensor.

FIG. 15 is a diagram illustrating example operational states of thesensor according to exemplary embodiments of the disclosed subjectmatter.

FIG. 16 is a diagram illustrating an example operational and data flowfor over-the-air programming of a sensor according to the disclosedsubject matter.

FIG. 17 is a diagram illustrating an example data flow for secureexchange of data between two devices according to the disclosed subjectmatter.

FIGS. 18A-18C show cross-sectional diagrams of analyte sensors includinga single active area.

FIGS. 19A-19C show cross-sectional diagrams of analyte sensors includingtwo active areas.

FIG. 20 shows a cross-sectional diagram of analyte sensors including twoactive areas.

FIGS. 21A-21C show perspective views of analyte sensors including twoactive areas disposed upon separate working electrodes.

FIG. 22 provides a cross-sectional diagram of an exemplary sensor thatincludes an NAD(P) depot for controlled NAD(P) release.

FIG. 23A provides a schematic of an exemplary analyte sensor thatincludes an NAD depot.

FIG. 23B provides a cross-sectional diagram of an exemplary analytesensor that excludes an NAD depot for use as a control.

FIG. 24 provides stability profiles of ketone detection over time withan analyte sensor that includes an NAD depot (as shown in FIG. 23A)compared to an analyte sensor that does not include an NAD depot (asshown in FIG. 23B).

DETAILED DESCRIPTION

The present disclosure is directed to analyte sensors comprising one ormore active areas that include a nicotinamide adenine dinucleotide (NAD)or nicotinamide adenine dinucleotide phosphate (NADP)-dependent enzyme(referred to herein collectively as an “NAD(P)-dependent enzyme”). Inparticular, analyte sensors of the present disclosure include aninternal reservoir of the cofactor NAD and/or NADP (referred to hereincollectively as “NAD(P)”) for the NAD(P)-dependent enzyme.

The use of an internal reservoir of NAD(P) within an analyte sensor canovercome some of the limitations associated with analyte sensors thatinclude an NAD(P)-dependent enzyme. For example, the amount of exogenousNAD(P) present in environment surrounding the sensor might not be insufficient quantities to support analyte sensor operation, which canresult in reduced sensitivity of the sensor. In addition, even ifsufficient exogenous NAD(P) exists in the environment surrounding theanalyte sensor, the molecular size of NAD(P) can prevent the moleculefrom diffusing through the surrounding sensor membrane to reach the oneor more NAD(P)-dependent enzymes present in the sensing chemistry layer,e.g., active areas, of the analyte sensor.

The present disclosure provides analyte sensors that include an internalsupply of NAD(P) that can release NAD(P) over an extended period of timeto allow monitoring of an analyte in vivo. In certain embodiments, theNAD(P) internal supply (also referred to herein as “an NAD(P) depot”)can be coated with or distributed within a permeable layer (e.g., apolymeric permeable layer) that controls diffusion of NAD(P) from theNAD(P) depot to maintain a sufficient concentration of NAD(P) for thesensing chemistry during use of the analyte sensor.

The present disclosure further provides methods of detecting an analyteusing the disclosed sensors and methods of manufacturing the disclosedanalyte sensors.

For clarity, but not by way of limitation, the detailed description ofthe presently disclosed subject matter is divided into the followingsubsections:

I. Definitions;

II. Analyte Sensors;

-   -   1. General Structure of Analyte Sensor Systems;    -   2. NAD(P)-depot;    -   3. Enzymes;    -   4. Redox Mediators;    -   5. Polymeric Backbone;    -   6. Mass Transport Limiting Membrane;    -   7. Interference Domain; and    -   8. Manufacturing;

III. Analyte Monitoring.

I. Definitions

The terms used in this specification generally have their ordinarymeanings in the art, within the context of this disclosure and in thespecific context where each term is used. Certain terms are discussedbelow, or elsewhere in the specification, to provide additional guidanceto the practitioner in describing the compositions and methods of thepresent disclosure and how to make and use them.

As used herein, the use of the word “a” or “an” when used in conjunctionwith the term “comprising” in the claims and/or the specification canmean “one,” but it is also consistent with the meaning of “one or more,”“at least one,” and “one or more than one.”

The terms “comprise(s),” “include(s),” “having,” “has,” “can,”“contain(s),” and variants thereof, as used herein, are intended to beopen-ended transitional phrases, terms or words that do not precludeadditional acts or structures. The present disclosure also contemplatesother embodiments “comprising,” “consisting of” and “consistingessentially of,” the embodiments or elements presented herein, whetherexplicitly set forth or not.

The term “about” or “approximately” means within an acceptable errorrange for the particular value as determined by one of ordinary skill inthe art, which depends in part on how the value is measured ordetermined, i.e., the limitations of the measurement system. Forexample, “about” can mean within 3 or more than 3 standard deviations,per the practice in the art. Alternatively, “about” can mean a range ofup to 20%, preferably up to 10%, more preferably up to 5%, and morepreferably still up to 1% of a given value. Alternatively, particularlywith respect to biological systems or processes, the term can meanwithin an order of magnitude, preferably within 5-fold, and morepreferably within 2-fold, of a value.

As used herein, “analyte sensor” or “sensor” can refer to any devicecapable of receiving sensor information from a user, including forpurpose of illustration but not limited to, body temperature sensors,blood pressure sensors, pulse or heart-rate sensors, glucose levelsensors, analyte sensors, physical activity sensors, body movementsensors, or any other sensors for collecting physical or biologicalinformation. Analytes measured by the analyte sensors can include, byway of example and not limitation, glucose, ketones, lactate, oxygen,hemoglobin A1C, albumin, alcohol, alkaline phosphatase, alaninetransaminase, aspartate aminotransferase, bilirubin, blood ureanitrogen, calcium, carbon dioxide, chloride, creatinine, hematocrit,lactate, magnesium, oxygen, pH, phosphorus, potassium, sodium, totalprotein, uric acid, etc.

The term “biological fluid,” as used herein, refers to any bodily fluidor bodily fluid derivative in which the analyte can be measured.Non-limiting examples of a biological fluid include dermal fluid,interstitial fluid, plasma, blood, lymph, synovial fluid, cerebrospinalfluid, saliva, bronchoalveolar lavage, amniotic fluid, sweat, tears orthe like. In certain embodiments, the biological fluid is dermal fluidor interstitial fluid. In certain embodiments, the biological fluid isinterstitial fluid.

The term “electrolysis,” as used herein, refers to electrooxidation orelectroreduction of a compound either directly at an electrode or viaone or more electron transfer agents (e.g., redox mediators or enzymes).

The terms “enzyme composition” and “sensing chemistry,” as usedinterchangeably herein, refer to a composition that includes one or moreenzymes for detecting and/or measuring an analyte. In certainnon-limiting embodiments, the enzyme compositions can include one ormore enzymes, polymers, redox mediators and/or crosslinkers.

As used herein, the term “homogenous membrane” refers to a membranecomprising a single type of membrane polymer.

As used herein, the term “multi-component membrane” refers to a membranecomprising two or more types of membrane polymers.

As used herein, the term “NAD(P)” refers to the cofactor NAD (and itsreduced form NADH) or NADP (and its reduced form NADPH) or a derivativethereof.

As used herein, the term “NAD(P)-dependent enzyme” refers to an enzymethat uses NAD (and its reduced form NADH) or NADP (and its reduced formNADPH) as a coenzyme in a redox reaction.

As used herein, the term “permeable electrode” refers to an electrodethat is composed of a material that allows the passing of molecules,e.g., NAD(P), through the material of the electrode.

As used herein, the term “polyvinylpyridine-based polymer” refers to apolymer or copolymer that comprises polyvinylpyridine (e.g.,poly(2-vinylpyridine) or poly(4-vinylpyridine)) or a derivative thereof.

As used herein, the term “redox mediator” refers to an electron transferagent for carrying electrons between an analyte or an analyte-reduced oranalyte oxidized enzyme and an electrode, either directly, or via one ormore additional electron transfer agents. In certain embodiments, redoxmediators that include a polymeric backbone can also be referred to as“redox polymers.”

The term “reference electrode” as used herein, can refer to eitherreference electrodes or electrodes that function as both, a referenceand a counter electrode. Similarly, the term “counter electrode,” asused herein, can refer to both, a counter electrode and a counterelectrode that also functions as a reference electrode.

II. Analyte Sensors

Before the present subject matter is described in detail, it is to beunderstood that this disclosure is not limited to the particularembodiments described, as such may, of course, vary. It is also to beunderstood that the terminology used herein is for the purpose ofdescribing particular embodiments only, and is not intended to belimiting, since the scope of the present disclosure will be limited onlyby the appended claims.

The publications discussed herein are provided solely for theirdisclosure prior to the filing date of the present application. Nothingherein is to be construed as an admission that the present disclosure isnot entitled to antedate such publication by virtue of prior disclosure.Further, the dates of publication provided may be different from theactual publication dates which may need to be independently confirmed.

Generally, embodiments of the present disclosure include systems,devices and methods for the use of analyte sensor insertion applicatorsfor use with in vivo analyte monitoring systems. An applicator can beprovided to the user in a sterile package with an electronics housing ofthe sensor control device contained therein. According to someembodiments, a structure separate from the applicator, such as acontainer, can also be provided to the user as a sterile package with asensor module and a sharp module contained therein. The user can couplethe sensor module to the electronics housing, and can couple the sharpto the applicator with an assembly process that involves the insertionof the applicator into the container in a specified manner. In otherembodiments, the applicator, sensor control device, sensor module, andsharp module can be provided in a single package. The applicator can beused to position the sensor control device on a human body with a sensorin contact with the wearer's bodily fluid. The embodiments providedherein are improvements to reduce the likelihood that a sensor isimproperly inserted or damaged, or elicits an adverse physiologicalresponse. Other improvements and advantages are provided as well. Thevarious configurations of these devices are described in detail by wayof the embodiments which are only examples.

Furthermore, many embodiments include in vivo analyte sensorsstructurally configured so that at least a portion of the sensor is, orcan be, positioned in the body of a user to obtain information about atleast one analyte of the body. It should be noted, however, that theembodiments disclosed herein can be used with in vivo analyte monitoringsystems that incorporate in vitro capability, as well as purely in vitroor ex vivo analyte monitoring systems, including systems that areentirely non-invasive.

Furthermore, for each and every embodiment of a method disclosed herein,systems and devices capable of performing each of those embodiments arecovered within the scope of the present disclosure. For example,embodiments of sensor control devices are disclosed and these devicescan have one or more sensors, analyte monitoring circuits (e.g., ananalog circuit), memories (e.g., for storing instructions), powersources, communication circuits, transmitters, receivers, processorsand/or controllers (e.g., for executing instructions) that can performany and all method steps or facilitate the execution of any and allmethod steps. These sensor control device embodiments can be used andcan be capable of use to implement those steps performed by a sensorcontrol device from any and all of the methods described herein.

Furthermore, the systems and methods presented herein can be used foroperations of a sensor used in an analyte monitoring system, such as butnot limited to wellness, fitness, dietary, research, information or anypurposes involving analyte sensing over time. As used herein, “analytesensor” or “sensor” can refer to any device capable of receiving sensorinformation from a user, including for purpose of illustration but notlimited to, body temperature sensors, blood pressure sensors, pulse orheart-rate sensors, glucose level sensors, analyte sensors, physicalactivity sensors, body movement sensors, or any other sensors forcollecting physical or biological information. In certain embodiments,an analyte sensor of the present disclosure can further measure analytesincluding, but not limited to, glucose, ketones, lactate, oxygen,hemoglobin A1C, albumin, alcohol, alkaline phosphatase, alaninetransaminase, aspartate aminotransferase, bilirubin, blood ureanitrogen, calcium, carbon dioxide, chloride, creatinine, hematocrit,lactate, magnesium, oxygen, pH, phosphorus, potassium, sodium, totalprotein, uric acid, etc.

As mentioned, a number of embodiments of systems, devices, and methodsare described herein that provide for the improved assembly and use ofdermal sensor insertion devices for use with in vivo analyte monitoringsystems. In particular, several embodiments of the present disclosureare designed to improve the method of sensor insertion with respect toin vivo analyte monitoring systems and, in particular, to prevent thepremature retraction of an insertion sharp during a sensor insertionprocess. Some embodiments, for example, include a dermal sensorinsertion mechanism with an increased firing velocity and a delayedsharp retraction. In other embodiments, the sharp retraction mechanismcan be motion-actuated such that the sharp is not retracted until theuser pulls the applicator away from the skin. Consequently, theseembodiments can reduce the likelihood of prematurely withdrawing aninsertion sharp during a sensor insertion process; decrease thelikelihood of improper sensor insertion; and decrease the likelihood ofdamaging a sensor during the sensor insertion process, to name a fewadvantages. Several embodiments of the present disclosure also providefor improved insertion sharp modules to account for the small scale ofdermal sensors and the relatively shallow insertion path present in asubject's dermal layer. In addition, several embodiments of the presentdisclosure are designed to prevent undesirable axial and/or rotationalmovement of applicator components during sensor insertion. Accordingly,these embodiments can reduce the likelihood of instability of apositioned dermal sensor, irritation at the insertion site, damage tosurrounding tissue, and breakage of capillary blood vessels resulting infouling of the dermal fluid with blood, to name a few advantages. Inaddition, to mitigate inaccurate sensor readings which can be caused bytrauma at the insertion site, several embodiments of the presentdisclosure can reduce the end-depth penetration of the needle relativeto the sensor tip during insertion.

Before describing these aspects of the embodiments in detail, however,it is first desirable to describe examples of devices that can bepresent within, for example, an in vivo analyte monitoring system, aswell as examples of their operation, all of which can be used with theembodiments described herein.

There are various types of in vivo analyte monitoring systems.“Continuous Analyte Monitoring” systems (or “Continuous GlucoseMonitoring” systems), for example, can transmit data from a sensorcontrol device to a reader device continuously without prompting, e.g.,automatically according to a schedule. “Flash Analyte Monitoring”systems (or “Flash Glucose Monitoring” systems or simply “Flash”systems), as another example, can transfer data from a sensor controldevice in response to a scan or request for data by a reader device,such as with a Near Field Communication (NFC) or Radio FrequencyIdentification (RFID) protocol. In vivo analyte monitoring systems canalso operate without the need for finger stick calibration.

In vivo analyte monitoring systems can be differentiated from “in vitro”systems that contact a biological sample outside of the body (or “exvivo”) and that typically include a meter device that has a port forreceiving an analyte test strip carrying bodily fluid of the user, whichcan be analyzed to determine the user's blood sugar level.

In vivo monitoring systems can include a sensor that, while positionedin vivo, makes contact with the bodily fluid of the user and senses theanalyte levels contained therein. The sensor can be part of the sensorcontrol device that resides on the body of the user and contains theelectronics and power supply that enable and control the analytesensing. The sensor control device, and variations thereof, can also bereferred to as a “sensor control unit,” an “on-body electronics” deviceor unit, an “on-body” device or unit, or a “sensor data communication”device or unit, to name a few.

In vivo monitoring systems can also include a device that receivessensed analyte data from the sensor control device and processes and/ordisplays that sensed analyte data, in any number of forms, to the user.This device, and variations thereof, can be referred to as a “handheldreader device,” “reader device” (or simply a “reader”), “handheldelectronics” (or simply a “handheld”), a “portable data processing”device or unit, a “data receiver,” a “receiver” device or unit (orsimply a “receiver”), or a “remote” device or unit, to name a few. Otherdevices such as personal computers have also been utilized with orincorporated into in vivo and in vitro monitoring systems.

1. General Structure of Analyte Sensor Systems

A. Exemplary In Vivo Analyte Monitoring System

FIG. 1A is a conceptual diagram depicting an example embodiment of ananalyte monitoring system 100 that includes a sensor applicator 150, asensor control device 102, and a reader device 120. Here, sensorapplicator 150 can be used to deliver sensor control device 102 to amonitoring location on a user's skin where a sensor 104 is maintained inposition for a period of time by an adhesive patch 105. Sensor controldevice 102 is further described in FIGS. 2B and 2C, and can communicatewith reader device 120 via a communication path or link 140 using awired or wireless, uni- or bi-directional, and encrypted ornon-encrypted technique. Example wireless protocols include Bluetooth,Bluetooth Low Energy (BLE, BTLE, Bluetooth SMART, etc.), Near FieldCommunication (NFC) and others. Users can monitor applications installedin memory on reader device 120 using screen 122 and input 121 and thedevice battery can be recharged using power port 123. More detail aboutreader device 120 is set forth with respect to FIG. 2A below. Readerdevice 120 can constitute an output medium for viewing analyteconcentrations and alerts or notifications determined by sensor 104 or aprocessor associated therewith, as well as allowing for one or more userinputs, according to certain embodiments. Reader device 120 can be amulti-purpose smartphone or a dedicated electronic reader instrument.While only one reader device 120 is shown, multiple reader devices 120can be present in certain instances.

Reader device 120 can communicate with local computer system 170 via acommunication path 141, which also can be wired or wireless, uni- orbi-directional, and encrypted or non-encrypted. Local computer system170 can include one or more of a laptop, desktop, tablet, phablet,smartphone, set-top box, video game console, remote terminal or othercomputing device and wireless communication can include any of a numberof applicable wireless networking protocols including Bluetooth,Bluetooth Low Energy (BTLE), Wi-Fi or others. Local computer system 170can communicate via communications path 143 with a network 190 similarto how reader device 120 can communicate via a communications path 142with network 190, by wired or wireless technique as describedpreviously. Network 190 can be any of a number of networks, such asprivate networks and public networks, local area or wide area networks,and so forth. A trusted computer system 180 can include a server and canprovide authentication services and secured data storage and cancommunicate via communications path 144 with network 190 by wired orwireless technique. Local computer system 170 and/or trusted computersystem 180 can be accessible, according to certain embodiments, byindividuals other than a primary user who have an interest in the user'sanalyte levels. Reader device 120 can include display 122 and optionalinput component 121. Display 122 can include a touch-screen interface,according to certain embodiments.

Sensor control device 102 includes sensor housing, which can housecircuitry and a power source for operating sensor 104. Optionally, thepower source and/or active circuitry can be omitted. A processor (notshown) can be communicatively coupled to sensor 104, with the processorbeing physically located within the sensor housing or reader device 120.Sensor 104 protrudes from the underside of the sensor housing andextends through adhesive layer 105, which is adapted for adhering thesensor housing to a tissue surface, such as skin, according to certainembodiments.

FIG. 1B illustrates an operating environment of an analyte monitoringsystem 100 a capable of embodying the techniques described herein. Theanalyte monitoring system 100 a can include a system of componentsdesigned to provide monitoring of parameters, such as analyte levels, ofa human or animal body or can provide for other operations based on theconfigurations of the various components. As embodied herein, the systemcan include a low-power analyte sensor 110, or simply “sensor” worn bythe user or attached to the body for which information is beingcollected. As embodied herein, the analyte sensor 110 can be a sealed,disposable device with a predetermined active use lifetime (e.g., 1 day,14 days, 30 days, etc.). Sensors 110 can be applied to the skin of theuser body and remain adhered over the duration of the sensor lifetime orcan be designed to be selectively removed and remain functional whenreapplied. The low-power analyte monitoring system 100 a can furtherinclude a data reading device 120 or multi-purpose data receiving device130 configured as described herein to facilitate retrieval and deliveryof data, including analyte data, from the analyte sensor 110.

As embodied herein, the analyte monitoring system 100 a can include asoftware or firmware library or application provided, for example via aremote application server 150 or application storefront server 160, to athird-party and incorporated into a multi-purpose hardware device 130such as a mobile phone, tablet, personal computing device, or othersimilar computing device capable of communicating with the analytesensor 110 over a communication link. Multi-purpose hardware can furtherinclude embedded devices, including, but not limited to insulin pumps orinsulin pens, having an embedded library configured to communicate withthe analyte sensor 110. Although the illustrated embodiments of theanalyte monitoring system 100 a include only one of each of theillustrated devices, this disclosure contemplates the analyte monitoringsystem 100 a incorporate multiples of each components interactingthroughout the system. For example and without limitation, as embodiedherein, data reading device 120 and/or multi-purpose data receivingdevice 130 can include multiples of each. As embodied herein, multipledata receiving devices 130 can communicate directly with sensor 110 asdescribed herein. Additionally or alternatively, a data receiving device130 can communicate with secondary data receiving devices 130 to provideanalyte data, or visualization or analysis of the data, for secondarydisplay to the user or other authorized parties.

Sensor 104 of FIG. 1A is adapted to be at least partially inserted intoa tissue of interest, such as within the dermal or subcutaneous layer ofthe skin. Sensor 104 can include a sensor tail of sufficient length forinsertion to a desired depth in a given tissue. The sensor tail caninclude at least one working electrode. In certain configurations, thesensor tail can include an active area, e.g., including one or moreNAD(P)-dependent enzymes, for detecting an analyte. A counter electrodecan be present in combination with the at least one working electrode.Particular electrode configurations upon the sensor tail are describedin more detail below.

One or more mass transport limiting membranes can overcoat the activearea, as also described in further detail below.

The active area can be configured for detecting a particular analytedescribed herein. For example, but not by way of the limitation, theanalyte can include glucose, ketones, lactate, oxygen, hemoglobin A1C,albumin, alcohol, alkaline phosphatase, alanine transaminase, aspartateaminotransferase, bilirubin, blood urea nitrogen, calcium, carbondioxide, chloride, creatinine, hematocrit, lactate, magnesium, oxygen,pH, phosphorus, potassium, sodium, total protein, uric acid, etc. Incertain embodiments, the analytes for detection using the disclosedanalyte sensors include alcohols, ketones, creatinine, glucose, andlactate. In certain embodiments, the active area can be configured fordetecting two or more analytes described herein. In certain embodiments,an active area of a presently disclosed sensor is configured to detectketones. In certain embodiments, an active area of a presently disclosedsensor is configured to detect glucose. In certain embodiments, anactive area of a presently disclosed sensor is configured to detectlactate. In certain embodiments, an active area of a presently disclosedsensor is configured to detect creatinine. In certain embodiments, anactive area of a presently disclosed sensor is configured to detect analcohol, e.g., ethanol.

In certain embodiments of the present disclosure, one or more analytescan be monitored in any biological fluid of interest such as dermalfluid, interstitial fluid, plasma, blood, lymph, synovial fluid,cerebrospinal fluid, saliva, bronchoalveolar lavage, amniotic fluid orthe like. In certain particular embodiments, analyte sensors of thepresent disclosure can be adapted for assaying dermal fluid orinterstitial fluid to determine a concentration of one or more analytesin vivo. In certain embodiments, the biological fluid is interstitialfluid.

An introducer can be present transiently to promote introduction ofsensor 104 into a tissue. In certain illustrative embodiments, theintroducer can include a needle or similar sharp. As would be readilyrecognized by a person skilled in the art, other types of introducers,such as sheaths or blades, can be present in alternative embodiments.More specifically, the needle or other introducer can transiently residein proximity to sensor 104 prior to tissue insertion and then bewithdrawn afterward. While present, the needle or other introducer canfacilitate insertion of sensor 104 into a tissue by opening an accesspathway for sensor 104 to follow. For example, and not by the way oflimitation, the needle can facilitate penetration of the epidermis as anaccess pathway to the dermis to allow implantation of sensor 104 to takeplace, according to one or more embodiments. After opening the accesspathway, the needle or other introducer can be withdrawn so that it doesnot represent a sharps hazard. In certain embodiments, suitable needlescan be solid or hollow, beveled or non-beveled, and/or circular ornon-circular in cross-section. In more particular non-limitingembodiments, suitable needles can be comparable in cross-sectionaldiameter and/or tip design to an acupuncture needle, which can have across-sectional diameter of about 250 microns. However, suitable needlescan have a larger or smaller cross-sectional diameter if needed forcertain particular applications.

In certain embodiments, a tip of the needle (while present) can beangled over the terminus of sensor 104, such that the needle penetratesa tissue first and opens an access pathway for sensor 104. In certainembodiments, sensor 104 can reside within a lumen or groove of theneedle, with the needle similarly opening an access pathway for sensor104. In either case, the needle is subsequently withdrawn afterfacilitating sensor insertion.

B. Exemplary Reader Device

FIG. 2A is a block diagram depicting an example embodiment of a readerdevice configured as a smartphone. Here, reader device 120 can include adisplay 122, input component 121, and a processing core 206 including acommunications processor 222 coupled with memory 223 and an applicationsprocessor 224 coupled with memory 225. Also included can be separatememory 230, RF transceiver 228 with antenna 229, and power supply 226with power management module 238. Further included can be amulti-functional transceiver 232 which can communicate over Wi-Fi, NFC,Bluetooth, BTLE, and GPS with an antenna 234. As understood by one ofskill in the art, these components are electrically and communicativelycoupled in a manner to make a functional device.

C. Exemplary Data Receiving Device Architecture

For purpose of illustration and not limitation, reference is made to theexemplary embodiment of a data receiving device 120 for use with thedisclosed subject matter as shown in FIG. 2B. The data receiving device120, and the related multi-purpose data receiving device 130, includescomponents germane to the discussion of the analyte sensor 110 and itsoperations and additional components can be included. In particularembodiments, the data receiving device 120 and multi-purpose datareceiving device 130 can be or include components provided by a thirdparty and are not necessarily restricted to include devices made by thesame manufacturer as the sensor 110.

As illustrated in FIG. 2B, the data receiving device 120 includes anASIC 4000 including a microcontroller 4010, memory 4020, and storage4030 and communicatively coupled with a communication module 4040. Powerfor the components of the data receiving device 120 can be delivered bya power module 4050, which as embodied herein can include a rechargeablebattery. The data receiving device 120 can further include a display4070 for facilitating review of analyte data received from an analytesensor 110 or other device (e.g., user device 140 or remote applicationserver 150). The data receiving device 120 can include separate userinterface components (e.g., physical keys, light sensors, microphones,etc.).

The communication module 4040 can include a BLE module 4041 and an NFCmodule 4042. The data receiving device 120 can be configured towirelessly couple with the analyte sensor 110 and transmit commands toand receive data from the analyte sensor 110. As embodied herein, thedata receiving device 120 can be configured to operate, with respect tothe analyte sensor 110 as described herein, as an NFC scanner and a BLEend point via specific modules (e.g., BLE module 4042 or NFC module4043) of the communication module 4040. For example, the data receivingdevice 120 can issue commands (e.g., activation commands for a databroadcast mode of the sensor; pairing commands to identify the datareceiving device 120) to the analyte sensor 110 using a first module ofthe communication module 4040 and receive data from and transmit data tothe analyte sensor 110 using a second module of the communication module4040. The data receiving device 120 can be configured for communicationwith a user device 140 via a Universal Serial Bus (USB) module 4045 ofthe communication module 4040.

As another example, the communication module 4040 can include, forexample, a cellular radio module 4044. The cellular radio module 4044can include one or more radio transceivers for communicating usingbroadband cellular networks, including, but not limited to thirdgeneration (3G), fourth generation (4G), and fifth generation (5G)networks. Additionally, the communication module 4040 of the datareceiving device 120 can include a Wi-Fi radio module 4043 forcommunication using a wireless local area network according to one ormore of the IEEE 802.11 standards (e.g., 802.11a, 802.11b, 802.11g,802.11n (aka Wi-Fi 4), 802.11ac (aka Wi-Fi 5), 802.11ax (aka Wi-Fi 6)).Using the cellular radio module 4044 or Wi-Fi radio module 4043, thedata receiving device 120 can communicate with the remote applicationserver 150 to receive analyte data or provide updates or input receivedfrom a user (e.g., through one or more user interfaces). Although notillustrated, the communication module 5040 of the analyte sensor 120 cansimilarly include a cellular radio module or Wi-Fi radio module.

As embodied herein, the on-board storage 4030 of the data receivingdevice 120 can store analyte data received from the analyte sensor 110.Further, the data receiving device 120, multi-purpose data receivingdevice 130, or a user device 140 can be configured to communicate with aremote application server 150 via a wide area network. As embodiedherein, the analyte sensor 110 can provide data to the data receivingdevice 120 or multi-purpose data receiving device 130. The datareceiving device 120 can transmit the data to the user computing device140. The user computing device 140 (or the multi-purpose data receivingdevice 130) can in turn transmit that data to a remote applicationserver 150 for processing and analysis.

As embodied herein, the data receiving device 120 can further includesensing hardware 4060 similar to, or expanded from, the sensing hardware5060 of the analyte sensor 110. In particular embodiments, the datareceiving device 120 can be configured to operate in coordination withthe analyte sensor 110 and based on analyte data received from theanalyte sensor 110. As an example, where the analyte sensor 110 glucosesensor, the data receiving device 120 can be or include an insulin pumpor insulin injection pen. In coordination, the compatible device 130 canadjust an insulin dosage for a user based on glucose values receivedfrom the analyte sensor.

D. Exemplary Sensor Control Devices

FIGS. 2C and 2D are block diagrams depicting example embodiments ofsensor control device 102 having analyte sensor 104 and sensorelectronics 160 (including analyte monitoring circuitry) that can havethe majority of the processing capability for rendering end-result datasuitable for display to the user. In FIG. 2C, a single semiconductorchip 161 is depicted that can be a custom application specificintegrated circuit (ASIC). Shown within ASIC 161 are certain high-levelfunctional units, including an analog front end (AFE) 162, powermanagement (or control) circuitry 164, processor 166, and communicationcircuitry 168 (which can be implemented as a transmitter, receiver,transceiver, passive circuit, or otherwise according to thecommunication protocol). In this embodiment, both AFE 162 and processor166 are used as analyte monitoring circuitry, but in other embodimentseither circuit can perform the analyte monitoring function. Processor166 can include one or more processors, microprocessors, controllers,and/or microcontrollers, each of which can be a discrete chip ordistributed amongst (and a portion of) a number of different chips.

A memory 163 is also included within ASIC 161 and can be shared by thevarious functional units present within ASIC 161, or can be distributedamongst two or more of them. Memory 163 can also be a separate chip.Memory 163 can be volatile and/or non-volatile memory. In thisembodiment, ASIC 161 is coupled with power source 170, which can be acoin cell battery, or the like. AFE 162 interfaces with in vivo analytesensor 104 and receives measurement data therefrom and outputs the datato processor 166 in digital form, which in turn processes the data toarrive at the end-result glucose discrete and trend values, etc. Thisdata can then be provided to communication circuitry 168 for sending, byway of antenna 171, to reader device 120 (not shown), for example, whereminimal further processing is needed by the resident softwareapplication to display the data.

FIG. 2D is similar to FIG. 2C but instead includes two discretesemiconductor chips 162 and 174, which can be packaged together orseparately. Here, AFE 162 is resident on ASIC 161. Processor 166 isintegrated with power management circuitry 164 and communicationcircuitry 168 on chip 174. AFE 162 includes memory 163 and chip 174includes memory 165, which can be isolated or distributed within. In oneexample embodiment, AFE 162 is combined with power management circuitry164 and processor 166 on one chip, while communication circuitry 168 ison a separate chip. In another example embodiment, both AFE 162 andcommunication circuitry 168 are on one chip, and processor 166 and powermanagement circuitry 164 are on another chip. It should be noted thatother chip combinations are possible, including three or more chips,each bearing responsibility for the separate functions described, orsharing one or more functions for fail-safe redundancy.

For purpose of illustration and not limitation, reference is made to theexemplary embodiment of an analyte sensor 110 for use with the disclosedsubject matter as shown in FIG. 2E. FIG. 2E illustrates a block diagramof an example analyte sensor 110 according to exemplary embodimentscompatible with the security architecture and communication schemesdescribed herein.

As embodied herein, the analyte sensor 110 can include anApplication-Specific Integrated Circuit (“ASIC”) 5000 communicativelycoupled with a communication module 5040. The ASIC 5000 can include amicrocontroller core 5010, on-board memory 5020, and storage memory5030. The storage memory 5030 can store data used in an authenticationand encryption security architecture. The storage memory 5030 can storeprogramming instructions for the sensor 110. As embodied herein, certaincommunication chipsets can be embedded in the ASIC 5000 (e.g., an NFCtransceiver 5025). The ASIC 5000 can receive power from a power module5050, such as an on-board battery or from an NFC pulse. The storagememory 5030 of the ASIC 5000 can be programmed to include informationsuch as an identifier for the sensor 110 for identification and trackingpurposes. The storage memory 5030 can also be programmed withconfiguration or calibration parameters for use by the sensor 110 andits various components. The storage memory 5030 can include rewritableor one-time programming (OTP) memory. The storage memory 5030 can beupdated using techniques described herein to extend the usefulness ofthe sensor 110.

As embodied herein, the communication module 5040 of the sensor 100 canbe or include one or more modules to support the analyte sensor 110communicating with other devices of the analyte monitoring system 100.As an example only and not by way of limitation, example communicationmodules 5040 can include a Bluetooth Low-Energy (“BLE”) module 5041 Asused throughout this disclosure, Bluetooth Low Energy (“BLE”) refers toa short-range communication protocol optimized to make pairing ofBluetooth devices simple for end users. The communication module 5040can transmit and receive data and commands via interaction withsimilarly-capable communication modules of a data receiving device 120or user device 140. The communication module 5040 can include additionalor alternative chipsets for use with similar short-range communicationschemes, such as a personal area network according to IEEE 802.15protocols, IEEE 802.11 protocols, infrared communications according tothe Infrared Data Association standards (IrDA), etc.

To perform its functionalities, the sensor 100 can further includesuitable sensing hardware 5060 appropriate to its function. As embodiedherein, the sensing hardware 5060 can include an analyte sensortranscutaneously or subcutaneously positioned in contact with a bodilyfluid of a subject. The analyte sensor can generate sensor datacontaining values corresponding to levels of one or more analytes withinthe bodily fluid.

E. Exemplary Assembly Processes for Sensor Control Devices

The components of sensor control device 102 can be acquired by a user inmultiple packages requiring final assembly by the user before deliveryto an appropriate user location. FIGS. 3A-3D depict an exampleembodiment of an assembly process for sensor control device 102 by auser, including preparation of separate components before coupling thecomponents in order to ready the sensor for delivery. FIGS. 3E-3F depictan example embodiment of delivery of sensor control device 102 to anappropriate user location by selecting the appropriate delivery locationand applying device 102 to the location.

FIG. 3A is a proximal perspective view depicting an example embodimentof a user preparing a container 810, configured here as a tray (althoughother packages can be used), for an assembly process. The user canaccomplish this preparation by removing lid 812 from tray 810 to exposeplatform 808, for instance by peeling a non-adhered portion of lid 812away from tray 810 such that adhered portions of lid 812 are removed.Removal of lid 812 can be appropriate in various embodiments so long asplatform 808 is adequately exposed within tray 810. Lid 812 can then beplaced aside.

FIG. 3B is a side view depicting an example embodiment of a userpreparing an applicator device 150 for assembly. Applicator device 150can be provided in a sterile package sealed by a cap 708. Preparation ofapplicator device 150 can include uncoupling housing 702 from cap 708 toexpose sheath 704 (FIG. 3C). This can be accomplished by unscrewing (orotherwise uncoupling) cap 708 from housing 702. Cap 708 can then beplaced aside.

FIG. 3C is a proximal perspective view depicting an example embodimentof a user inserting an applicator device 150 into a tray 810 during anassembly. Initially, the user can insert sheath 704 into platform 808inside tray 810 after aligning housing orienting feature 1302 (or slotor recess) and tray orienting feature 924 (an abutment or detent).Inserting sheath 704 into platform 808 temporarily unlocks sheath 704relative to housing 702 and also temporarily unlocks platform 808relative to tray 810. At this stage, removal of applicator device 150from tray 810 will result in the same state prior to initial insertionof applicator device 150 into tray 810 (i.e., the process can bereversed or aborted at this point and then repeated withoutconsequence).

Sheath 704 can maintain position within platform 808 with respect tohousing 702 while housing 702 is distally advanced, coupling withplatform 808 to distally advance platform 808 with respect to tray 810.This step unlocks and collapses platform 808 within tray 810. Sheath 704can contact and disengage locking features (not shown) within tray 810that unlock sheath 704 with respect to housing 702 and prevent sheath704 from moving (relatively) while housing 702 continues to distallyadvance platform 808. At the end of advancement of housing 702 andplatform 808, sheath 704 is permanently unlocked relative to housing702. A sharp and sensor (not shown) within tray 810 can be coupled withan electronics housing (not shown) within housing 702 at the end of thedistal advancement of housing 702. Operation and interaction of theapplicator device 150 and tray 810 are further described below.

FIG. 3D is a proximal perspective view depicting an example embodimentof a user removing an applicator device 150 from a tray 810 during anassembly. A user can remove applicator 150 from tray 810 by proximallyadvancing housing 702 with respect to tray 810 or other motions havingthe same end effect of uncoupling applicator 150 and tray 810. Theapplicator device 150 is removed with sensor control device 102 (notshown) fully assembled (sharp, sensor, electronics) therein andpositioned for delivery.

FIG. 3E is a proximal perspective view depicting an example embodimentof a patient applying sensor control device 102 using applicator device150 to a target area of skin, for instance, on an abdomen or otherappropriate location. Advancing housing 702 distally collapses sheath704 within housing 702 and applies the sensor to the target locationsuch that an adhesive layer on the bottom side of sensor control device102 adheres to the skin. The sharp is automatically retracted whenhousing 702 is fully advanced, while the sensor (not shown) is left inposition to measure analyte levels.

FIG. 3F is a proximal perspective view depicting an example embodimentof a patient with sensor control device 102 in an applied position. Theuser can then remove applicator 150 from the application site.

System 100, described with respect to FIGS. 3A-3F and elsewhere herein,can provide a reduced or eliminated chance of accidental breakage,permanent deformation, or incorrect assembly of applicator componentscompared to prior art systems. Since applicator housing 702 directlyengages platform 808 while sheath 704 unlocks, rather than indirectengagement via sheath 704, relative angularity between sheath 704 andhousing 702 will not result in breakage or permanent deformation of thearms or other components. The potential for relatively high forces (suchas in conventional devices) during assembly will be reduced, which inturn reduces the chance of unsuccessful user assembly.

F. Exemplary Sensor Applicator Devices

FIG. 4A is a side view depicting an example embodiment of an applicatordevice 150 coupled with screw cap 708. This is an example of howapplicator 150 is shipped to and received by a user, prior to assemblyby the user with a sensor. FIG. 4B is a side perspective view depictingapplicator 150 and cap 708 after being decoupled. FIG. 4C is aperspective view depicting an example embodiment of a distal end of anapplicator device 150 with electronics housing 706 and adhesive patch105 removed from the position they would have retained within sensorcarrier 710 of sheath 704, when cap 708 is in place.

Referring to FIG. 4D-G for purpose of illustration and not limitation,the applicator device 20150 can be provided to a user as a singleintegrated assembly. FIGS. 4D and 4E provide perspective top and bottomviews, respectively, of the applicator device 20150, FIG. 4F provides anexploded view of the applicator device 20150 and FIG. 4G provides a sidecut-away view. The perspective views illustrate how applicator 20150 isshipped to and received by a user. The exploded and cut-away viewsillustrate the components of the applicator device 20150. The applicatordevice 20150 can include a housing 20702, gasket 20701, sheath 20704,sharp carrier 201102, spring 205612, sensor carrier 20710 (also referredto as a “puck carrier”), sharp hub 205014, sensor control device (alsoreferred to as a “puck”) 20102, adhesive patch 20105, desiccant 20502,cap 20708, serial label 20709, and tamper evidence feature 20712. Asreceived by a user, only the housing 20702, cap 20708, tamper evidencefeature 20712, and label 20709 are visible. The tamper evidence feature20712 can be, for example, a sticker coupled to each of the housing20702 and the cap 20708, and tamper evidence feature 20712 can bedamaged, for example, irreparably, by uncoupling housing 20702 and cap20708, thereby indicating to a user that the housing 20702 and cap 20708have been previously uncoupled. These features are described in greaterdetail below.

G. Exemplary Tray and Sensor Module Assembly

FIG. 5 is a proximal perspective view depicting an example embodiment ofa tray 810 with sterilization lid 812 removably coupled thereto, whichmay be representative of how the package is shipped to and received by auser prior to assembly.

FIG. 6A is a proximal perspective cutaway view depicting sensor deliverycomponents within tray 810. Platform 808 is slidably coupled within tray810. Desiccant 502 is stationary with respect to tray 810. Sensor module504 is mounted within tray 810.

FIG. 6B is a proximal perspective view depicting sensor module 504 ingreater detail. Here, retention arm extensions 1834 of platform 808releasably secure sensor module 504 in position. Module 2200 is coupledwith connector 2300, sharp module 2500 and sensor (not shown) such thatduring assembly they can be removed together as sensor module 504.

H. Exemplary Applicators and Sensor Control Devices for One PieceArchitectures

Referring briefly again to FIGS. 1A and 3A-3G, for the two-piecearchitecture system, the sensor tray 202 and the sensor applicator 102are provided to the user as separate packages, thus requiring the userto open each package and finally assemble the system. In someapplications, the discrete, sealed packages allow the sensor tray 202and the sensor applicator 102 to be sterilized in separate sterilizationprocesses unique to the contents of each package and otherwiseincompatible with the contents of the other. More specifically, thesensor tray 202, which includes the plug assembly 207, including thesensor 110 and the sharp 220, may be sterilized using radiationsterilization, such as electron beam (or “e-beam”) irradiation. Suitableradiation sterilization processes include, but are not limited to,electron beam (e-beam) irradiation, gamma ray irradiation, X-rayirradiation, or any combination thereof. Radiation sterilization,however, can damage the electrical components arranged within theelectronics housing of the sensor control device 102. Consequently, ifthe sensor applicator 102, which contains the electronics housing of thesensor control device 102, needs to be sterilized, it may be sterilizedvia another method, such as gaseous chemical sterilization using, forexample, ethylene oxide. Gaseous chemical sterilization, however, candamage the enzymes or other chemistry and biologies included on thesensor 110. Because of this sterilization incompatibility, the sensortray 202 and the sensor applicator 102 are commonly sterilized inseparate sterilization processes and subsequently packaged separately,which requires the user to finally assemble the components for use.

FIGS. 7A and 7B are exploded top and bottom views, respectively, of thesensor control device 3702, according to one or more embodiments. Theshell 3706 and the mount 3708 operate as opposing clamshell halves thatenclose or otherwise substantially encapsulate the various electroniccomponents of the sensor control device 3702. As illustrated, the sensorcontrol device 3702 may include a printed circuit board assembly (PCBA)3802 that includes a printed circuit board (PCB) 3804 having a pluralityof electronic modules 3806 coupled thereto. Example electronic modules3806 include, but are not limited to, resistors, transistors,capacitors, inductors, diodes, and switches. Prior sensor controldevices commonly stack PCB components on only one side of the PCB. Incontrast, the PCB components 3806 in the sensor control device 3702 canbe dispersed about the surface area of both sides (i.e., top and bottomsurfaces) of the PCB 3804.

Besides the electronic modules 3806, the PCBA 3802 may also include adata processing unit 3808 mounted to the PCB 3804. The data processingunit 3808 may comprise, for example, an application specific integratedcircuit (ASIC) configured to implement one or more functions or routinesassociated with operation of the sensor control device 3702. Morespecifically, the data processing unit 3808 may be configured to performdata processing functions, where such functions may include but are notlimited to, filtering and encoding of data signals, each of whichcorresponds to a sampled analyte level of the user. The data processingunit 3808 may also include or otherwise communicate with an antenna forcommunicating with the reader device 106 (FIG. 1A).

A battery aperture 3810 may be defined in the PCB 3804 and sized toreceive and seat a battery 3812 configured to power the sensor controldevice 3702. An axial battery contact 3814 a and a radial batterycontact 3814 b may be coupled to the PCB 3804 and extend into thebattery aperture 3810 to facilitate transmission of electrical powerfrom the battery 3812 to the PCB 3804. As their names suggest, the axialbattery contact 3814 a may be configured to provide an axial contact forthe battery 3812, while the radial battery contact 3814 b may provide aradial contact for the battery 3812. Locating the battery 3812 withinthe battery aperture 3810 with the battery contacts 3814 a,b helpsreduce the height H of the sensor control device 3702, which allows thePCB 3804 to be located centrally and its components to be dispersed onboth sides (i.e., top and bottom surfaces). This also helps facilitatethe chamfer 3718 provided on the electronics housing 3704.

The sensor 3716 may be centrally located relative to the PCB 3804 andinclude a tail 3816, a flag 3818, and a neck 3820 that interconnects thetail 3816 and the flag 3818. The tail 3816 may be configured to extendthrough the central aperture 3720 of the mount 3708 to betranscutaneously received beneath a user's skin. Moreover, the tail 3816may have an enzyme or other chemistry included thereon to helpfacilitate analyte monitoring.

The flag 3818 may include a generally planar surface having one or moresensor contacts 3822 (three shown in FIG. 7B) arranged thereon. Thesensor contact(s) 3822 may be configured to align with and engage acorresponding one or more circuitry contacts 3824 (three shown in FIG.7A) provided on the PCB 3804. In some embodiments, the sensor contact(s)3822 may comprise a carbon impregnated polymer printed or otherwisedigitally applied to the flag 3818. Prior sensor control devicestypically include a connector made of silicone rubber that encapsulatesone or more compliant carbon impregnated polymer modules that serve aselectrical conductive contacts between the sensor and the PCB. Incontrast, the presently disclosed sensor contacts(s) 3822 provide adirect connection between the sensor 3716 and the PCB 3804 connection,which eliminates the need for the prior art connector and advantageouslyreduces the height H. Moreover, eliminating the compliant carbonimpregnated polymer modules eliminates a significant circuit resistanceand therefor improves circuit conductivity.

The sensor control device 3702 may further include a compliant member3826, which may be arranged to interpose the flag 3818 and the innersurface of the shell 3706. More specifically, when the shell 3706 andthe mount 3708 are assembled to one another, the compliant member 3826may be configured to provide a passive biasing load against the flag3818 that forces the sensor contact(s) 3822 into continuous engagementwith the corresponding circuitry contact(s) 3824. In the illustratedembodiment, the compliant member 3826 is an elastomeric O-ring, butcould alternatively comprise any other type of biasing device ormechanism, such as a compression spring or the like, without departingfrom the scope of the disclosure.

The sensor control device 3702 may further include one or moreelectromagnetic shields, shown as a first shield 3828 a and a secondshield The shell 3706 may provide or otherwise define a first clockingreceptacle 3830 a (FIG. 7B) and a second clocking receptacle 3830 b(FIG. 7B), and the mount 3708 may provide or otherwise define a firstclocking post 3832 a (FIG. 7A) and a second clocking post 3832 b (FIG.7A). Mating the first and second clocking receptacles 3830 a,b with thefirst and second clocking posts 3832 a,b, respectively, will properlyalign the shell 3706 to the mount 3708.

Referring specifically to FIG. 7A, the inner surface of the mount 3708may provide or otherwise define a plurality of pockets or depressionsconfigured to accommodate various component parts of the sensor controldevice 3702 when the shell 3706 is mated to the mount 3708. For example,the inner surface of the mount 3708 may define a battery locator 3834configured to accommodate a portion of the battery 3812 when the sensorcontrol device 3702 is assembled. An adjacent contact pocket 3836 may beconfigured to accommodate a portion of the axial contact 3814 a.

Moreover, a plurality of module pockets 3838 may be defined in the innersurface of the mount 3708 to accommodate the various electronic modules3806 arranged on the bottom of the PCB 3804. Furthermore, a shieldlocator 3840 may be defined in the inner surface of the mount 3708 toaccommodate at least a portion of the second shield 3828 b when thesensor control device 3702 is assembled. The battery locator 3834, thecontact pocket 3836, the module pockets 3838, and the shield locator3840 all extend a short distance into the inner surface of the mount3708 and, as a result, the overall height H of the sensor control device3702 may be reduced as compared to prior sensor control devices. Themodule pockets 3838 may also help minimize the diameter of the PCB 3804by allowing PCB components to be arranged on both sides (i.e., top andbottom surfaces).

Still referring to FIG. 7A, the mount 3708 may further include aplurality of carrier grip features 3842 (two shown) defined about theouter periphery of the mount 3708. The carrier grip features 3842 areaxially offset from the bottom 3844 of the mount 3708, where a transferadhesive (not shown) may be applied during assembly. In contrast toprior sensor control devices, which commonly include conical carriergrip features that intersect with the bottom of the mount, the presentlydisclosed carrier grip features 3842 are offset from the plane (i.e.,the bottom 3844) where the transfer adhesive is applied. This may proveadvantageous in helping ensure that the delivery system does notinadvertently stick to the transfer adhesive during assembly. Moreover,the presently disclosed carrier grip features 3842 eliminate the needfor a scalloped transfer adhesive, which simplifies the manufacture ofthe transfer adhesive and eliminates the need to accurately clock thetransfer adhesive relative to the mount 3708. This also increases thebond area and, therefore, the bond strength.

Referring to FIG. 7B, the bottom 3844 of the mount 3708 may provide orotherwise define a plurality of grooves 3846, which may be defined at ornear the outer periphery of the mount 3708 and equidistantly spaced fromeach other. A transfer adhesive (not shown) may be coupled to the bottom3844 and the grooves 3846 may be configured to help convey (transfer)moisture away from the sensor control device 3702 and toward theperiphery of the mount 3708 during use. In some embodiments, the spacingof the grooves 3846 may interpose the module pockets 3838 (FIG. 7A)defined on the opposing side (inner surface) of the mount 3708. As willbe appreciated, alternating the position of the grooves 3846 and themodule pockets 3838 ensures that the opposing features on either side ofthe mount 3708 do not extend into each other. This may help maximizeusage of the material for the mount 3708 and thereby help maintain aminimal height H of the sensor control device 3702. The module pockets3838 may also significantly reduce mold sink, and improve the flatnessof the bottom 3844 that the transfer adhesive bonds to.

Still referring to FIG. 7B, the inner surface of the shell 3706 may alsoprovide or otherwise define a plurality of pockets or depressionsconfigured to accommodate various component parts of the sensor controldevice 3702 when the shell 3706 is mated to the mount 3708. For example,the inner surface of the shell 3706 may define an opposing batterylocator 3848 arrangeable opposite the battery locator 3834 (FIG. 7A) ofthe mount 3708 and configured to accommodate a portion of the battery3812 when the sensor control device 3702 is assembled. The opposingbattery locator 3848 extends a short distance into the inner surface ofthe shell 3706, which helps reduce the overall height H of the sensorcontrol device 3702.

A sharp and sensor locator 3852 may also be provided by or otherwisedefined on the inner surface of the shell 3706. The sharp and sensorlocator 3852 may be configured to receive both the sharp (not shown) anda portion of the sensor 3716. Moreover, the sharp and sensor locator3852 may be configured to align and/or mate with a corresponding sharpand sensor locator 2054 (FIG. 7A) provided on the inner surface of themount 3708.

According to embodiments of the present disclosure, an alternativesensor assembly/electronics assembly connection approach is illustratedin FIGS. 8A to 8C. As shown, the sensor assembly 14702 includes sensor14704, connector support 14706, and sharp 14708. Notably, a recess orreceptacle 14710 may be defined in the bottom of the mount of theelectronics assembly 14712 and provide a location where the sensorassembly 14702 may be received and coupled to the electronics assembly14712, and thereby fully assemble the sensor control device. The profileof the sensor assembly 14702 may match or be shaped in complementaryfashion to the receptacle 14710, which includes an elastomeric sealingmember 14714 (including conductive material coupled to the circuit boardand aligned with the electrical contacts of the sensor 14704). Thus,when the sensor assembly 14702 is snap fit or otherwise adhered to theelectronics assembly 14712 by driving the sensor assembly 14702 into theintegrally formed recess 14710 in the electronics assembly 14712, theon-body device 14714 depicted in FIG. 8C is formed. This embodimentprovides an integrated connector for the sensor assembly 14702 withinthe electronics assembly 14712.

Additional information regarding sensor assemblies is provided in U.S.Publication No. 2013/0150691 and U.S. Publication No. 2021/0204841, eachof which is incorporated by reference herein in its entirety.

According to embodiments of the present disclosure, the sensor controldevice 102 may be modified to provide a one-piece architecture that maybe subjected to sterilization techniques specifically designed for aone-piece architecture sensor control device. A one-piece architectureallows the sensor applicator 150 and the sensor control device 102 to beshipped to the user in a single, sealed package that does not requireany final user assembly steps. Rather, the user need only open onepackage and subsequently deliver the sensor control device 102 to thetarget monitoring location. The one-piece system architecture describedherein may prove advantageous in eliminating component parts, variousfabrication process steps, and user assembly steps. As a result,packaging and waste are reduced, and the potential for user error orcontamination to the system is mitigated.

FIGS. 9A and 9B are side and cross-sectional side views, respectively,of an example embodiment of the sensor applicator 102 with theapplicator cap 210 coupled thereto. More specifically, FIG. 9A depictshow the sensor applicator 102 might be shipped to and received by auser, and FIG. 9B depicts the sensor control device 4402 arranged withinthe sensor applicator 102. Accordingly, the fully assembled sensorcontrol device 4402 may already be assembled and installed within thesensor applicator 102 prior to being delivered to the user, thusremoving any additional assembly steps that a user would otherwise haveto perform.

The fully assembled sensor control device 4402 may be loaded into thesensor applicator 102, and the applicator cap 210 may subsequently becoupled to the sensor applicator 102. In some embodiments, theapplicator cap 210 may be threaded to the housing 208 and include atamper ring 4702. Upon rotating (e.g., unscrewing) the applicator cap210 relative to the housing 208, the tamper ring 4702 may shear andthereby free the applicator cap 210 from the sensor applicator 102.

According to the present disclosure, while loaded in the sensorapplicator 102, the sensor control device 4402 may be subjected togaseous chemical sterilization 4704 configured to sterilize theelectronics housing 4404 and any other exposed portions of the sensorcontrol device 4402. To accomplish this, a chemical may be injected intoa sterilization chamber 4706 cooperatively defined by the sensorapplicator 102 and the interconnected cap 210. In some applications, thechemical may be injected into the sterilization chamber 4706 via one ormore vents 4708 defined in the applicator cap 210 at its proximal end610. Example chemicals that may be used for the gaseous chemicalsterilization 4704 include, but are not limited to, ethylene oxide,vaporized hydrogen peroxide, nitrogen oxide (e.g., nitrous oxide,nitrogen dioxide, etc.), and steam.

Since the distal portions of the sensor 4410 and the sharp 4412 aresealed within the sensor cap 4416, the chemicals used during the gaseouschemical sterilization process do not interact with the enzymes,chemistry, and biologics provided on the tail 4524 and other sensorcomponents, such as membrane coatings that regulate analyte influx.

Once a desired sterility assurance level has been achieved within thesterilization chamber 4706, the gaseous solution may be removed and thesterilization chamber 4706 may be aerated. Aeration may be achieved by aseries of vacuums and subsequently circulating a gas (e.g., nitrogen) orfiltered air through the sterilization chamber 4706. Once thesterilization chamber 4706 is properly aerated, the vents 4708 may beoccluded with a seal 4712 (shown in dashed lines).

In some embodiments, the seal 4712 may comprise two or more layers ofdifferent materials. The first layer may be made of a synthetic material(e.g., a flash-spun high-density polyethylene fiber), such as Tyvek®available from DuPont®. Tyvek® is highly durable and puncture resistantand allows the permeation of vapors. The Tyvek® layer can be appliedbefore the gaseous chemical sterilization process, and following thegaseous chemical sterilization process, a foil or other vapor andmoisture resistant material layer may be sealed (e.g., heat sealed) overthe Tyvek® layer to prevent the ingress of contaminants and moistureinto the sterilization chamber 4706. In other embodiments, the seal 4712may comprise only a single protective layer applied to the applicatorcap 210. In such embodiments, the single layer may be gas permeable forthe sterilization process, but may also be capable of protection againstmoisture and other harmful elements once the sterilization process iscomplete.

With the seal 4712 in place, the applicator cap 210 provides a barrieragainst outside contamination, and thereby maintains a sterileenvironment for the assembled sensor control device 4402 until the userremoves (unthreads) the applicator cap 210. The applicator cap 210 mayalso create a dust-free environment during shipping and storage thatprevents the adhesive patch 4714 from becoming dirty.

FIGS. 10A and 10B are isometric and side views, respectively, of anotherexample sensor control device 5002, according to one or more embodimentsof the present disclosure. The sensor control device 5002 may be similarin some respects to the sensor control device 102 of FIG. 1A andtherefore may be best understood with reference thereto. Moreover, thesensor control device 5002 may replace the sensor control device 102 ofFIG. 1A and, therefore, may be used in conjunction with the sensorapplicator 102 of FIG. 1A, which may deliver the sensor control device5002 to a target monitoring location on a user's skin.

Unlike the sensor control device 102 of FIG. 1A, however, the sensorcontrol device 5002 may comprise a one-piece system architecture notrequiring a user to open multiple packages and finally assemble thesensor control device 5002 prior to application. Rather, upon receipt bythe user, the sensor control device 5002 may already be fully assembledand properly positioned within the sensor applicator 150 (FIG. 1A). Touse the sensor control device 5002, the user need only open one barrier(e.g., the applicator cap 708 of FIG. 3B) before promptly delivering thesensor control device 5002 to the target monitoring location for use.

As illustrated, the sensor control device 5002 includes an electronicshousing 5004 that is generally disc-shaped and may have a circularcross-section. In other embodiments, however, the electronics housing5004 may exhibit other cross-sectional shapes, such as ovoid orpolygonal, without departing from the scope of the disclosure. Theelectronics housing 5004 may be configured to house or otherwise containvarious electrical components used to operate the sensor control device5002. In at least one embodiment, an adhesive patch (not shown) may bearranged at the bottom of the electronics housing 5004. The adhesivepatch may be similar to the adhesive patch 105 of FIG. 1A, and may thushelp adhere the sensor control device 5002 to the user's skin for use.

As illustrated, the sensor control device 5002 includes an electronicshousing 5004 that includes a shell 5006 and a mount 5008 that is matablewith the shell 5006. The shell 5006 may be secured to the mount 5008 viaa variety of ways, such as a snap fit engagement, an interference fit,sonic welding, one or more mechanical fasteners (e.g., screws), agasket, an adhesive, or any combination thereof. In some cases, theshell 5006 may be secured to the mount 5008 such that a sealed interfaceis generated therebetween.

The sensor control device 5002 may further include a sensor 5010(partially visible) and a sharp 5012 (partially visible), used to helpdeliver the sensor 5010 transcutaneously under a user's skin duringapplication of the sensor control device 5002. As illustrated,corresponding portions of the sensor 5010 and the sharp 5012 extenddistally from the bottom of the electronics housing 5004 (e.g., themount 5008). The sharp 5012 may include a sharp hub 5014 configured tosecure and carry the sharp 5012. As best seen in FIG. 10B, the sharp hub5014 may include or otherwise define a mating member 5016. To couple thesharp 5012 to the sensor control device 5002, the sharp 5012 may beadvanced axially through the electronics housing 5004 until the sharphub 5014 engages an upper surface of the shell 5006 and the matingmember 5016 extends distally from the bottom of the mount 5008. As thesharp 5012 penetrates the electronics housing 5004, the exposed portionof the sensor 5010 may be received within a hollow or recessed (arcuate)portion of the sharp 5012. The remaining portion of the sensor 5010 isarranged within the interior of the electronics housing 5004.

The sensor control device 5002 may further include a sensor cap 5018,shown exploded or detached from the electronics housing 5004 in FIGS.10A-10B. The sensor cap 5016 may be removably coupled to the sensorcontrol device 5002 (e.g., the electronics housing 5004) at or near thebottom of the mount 5008. The sensor cap 5018 may help provide a sealedbarrier that surrounds and protects the exposed portions of the sensor5010 and the sharp 5012 from gaseous chemical sterilization. Asillustrated, the sensor cap 5018 may comprise a generally cylindricalbody having a first end 5020 a and a second end 5020 b opposite thefirst end 5020 a. The first end 5020 a may be open to provide accessinto an inner chamber 5022 defined within the body. In contrast, thesecond end 5020 b may be closed and may provide or otherwise define anengagement feature 5024. As described herein, the engagement feature5024 may help mate the sensor cap 5018 to the cap (e.g., the applicatorcap 708 of FIG. 3B) of a sensor applicator (e.g., the sensor applicator150 of FIGS. 1 and 3A-3G), and may help remove the sensor cap 5018 fromthe sensor control device 5002 upon removing the cap from the sensorapplicator.

The sensor cap 5018 may be removably coupled to the electronics housing5004 at or near the bottom of the mount 5008. More specifically, thesensor cap 5018 may be removably coupled to the mating member 5016,which extends distally from the bottom of the mount 5008. In at leastone embodiment, for example, the mating member 5016 may define a set ofexternal threads 5026 a (FIG. 10B) matable with a set of internalthreads 5026 b (FIG. 10A) defined by the sensor cap 5018. In someembodiments, the external and internal threads 5026 a, b may comprise aflat thread design (e.g., lack of helical curvature), which may proveadvantageous in molding the parts. Alternatively, the external andinternal threads 5026 a,b may comprise a helical threaded engagement.Accordingly, the sensor cap 5018 may be threadably coupled to the sensorcontrol device 5002 at the mating member 5016 of the sharp hub 5014. Inother embodiments, the sensor cap 5018 may be removably coupled to themating member 5016 via other types of engagements including, but notlimited to, an interference or friction fit, or a frangible member orsubstance that may be broken with minimal separation force (e.g., axialor rotational force).

In some embodiments, the sensor cap 5018 may comprise a monolithic(singular) structure extending between the first and second ends 5020 a,b. In other embodiments, however, the sensor cap 5018 may comprise twoor more component parts. In the illustrated embodiment, for example, thesensor cap 5018 may include a seal ring 5028 positioned at the first end5020 a and a desiccant cap 5030 arranged at the second end 5020 b. Theseal ring 5028 may be configured to help seal the inner chamber 5022, asdescribed in more detail below. In at least one embodiment, the sealring 5028 may comprise an elastomeric O-ring. The desiccant cap 5030 mayhouse or comprise a desiccant to help maintain preferred humidity levelswithin the inner chamber 5022. The desiccant cap 5030 may also define orotherwise provide the engagement feature 5024 of the sensor cap 5018.

FIGS. 11A-11C are progressive cross-sectional side views showingassembly of the sensor applicator 102 with the sensor control device5002, according to one or more embodiments. Once the sensor controldevice 5002 is fully assembled, it may then be loaded into the sensorapplicator 102. With reference to FIG. 11A, the sharp hub 5014 mayinclude or otherwise define a hub snap pawl 5302 configured to helpcouple the sensor control device 5002 to the sensor applicator 102. Morespecifically, the sensor control device 5002 may be advanced into theinterior of the sensor applicator 102 and the hub snap pawl 5302 may bereceived by corresponding arms 5304 of a sharp carrier 5306 positionedwithin the sensor applicator 102.

In FIG. 11B, the sensor control device 5002 is shown received by thesharp carrier 5306 and, therefore, secured within the sensor applicator102. Once the sensor control device 5002 is loaded into the sensorapplicator 102, the applicator cap 210 may be coupled to the sensorapplicator 102. In some embodiments, the applicator cap 210 and thehousing 208 may have opposing, matable sets of threads 5308 that enablethe applicator cap 210 to be screwed onto the housing 208 in a clockwise(or counter-clockwise) direction and thereby secure the applicator cap210 to the sensor applicator 102.

As illustrated, the sheath 212 is also positioned within the sensorapplicator 102, and the sensor applicator 102 may include a sheathlocking mechanism 5310 configured to ensure that the sheath 212 does notprematurely collapse during a shock event. In the illustratedembodiment, the sheath locking mechanism 5310 may comprise a threadedengagement between the applicator cap 210 and the sheath 212. Morespecifically, one or more internal threads 5312 a may be defined orotherwise provided on the inner surface of the applicator cap 210, andone or more external threads 53 12 b may be defined or otherwiseprovided on the sheath 212. The internal and external threads 53 12 a,bmay be configured to threadably mate as the applicator cap 210 isthreaded to the sensor applicator 102 at the threads 5308. The internaland external threads 5312 a,b may have the same thread pitch as thethreads 5308 that enable the applicator cap 210 to be screwed onto thehousing 208.

In FIG. 11C, the applicator cap 210 is shown fully threaded (coupled) tothe housing 208. As illustrated, the applicator cap 210 may furtherprovide and otherwise define a cap post 5314 centrally located withinthe interior of the applicator cap 210 and extending proximally from thebottom thereof. The cap post 5314 may be configured to receive at leasta portion of the sensor cap 5018 as the applicator cap 210 is screwedonto the housing 208.

With the sensor control device 5002 loaded within the sensor applicator102 and the applicator cap 210 properly secured, the sensor controldevice 5002 may then be subjected to a gaseous chemical sterilizationconfigured to sterilize the electronics housing 5004 and any otherexposed portions of the sensor control device 5002. Since the distalportions of the sensor 5010 and the sharp 5012 are sealed within thesensor cap 5018, the chemicals used during the gaseous chemicalsterilization process are unable to interact with the enzymes,chemistry, and biologies provided on the tail 5104, and other sensorcomponents, such as membrane coatings that regulate analyte influx.

FIGS. 12A-12C are progressive cross-sectional side views showingassembly and disassembly of an alternative embodiment of the sensorapplicator 102 with the sensor control device 5002, according to one ormore additional embodiments. A fully assembled sensor control device5002 may be loaded into the sensor applicator 102 by coupling the hubsnap pawl 5302 into the arms 5304 of the sharp carrier 5306 positionedwithin the sensor applicator 102, as generally described above.

In the illustrated embodiment, the sheath arms 5604 of the sheath 212may be configured to interact with a first detent 5702 a and a seconddetent 5702 b defined within the interior of the housing 208. The firstdetent 5702 a may alternately be referred to a “locking” detent, and thesecond detent 5702 b may alternately be referred to as a “firing”detent. When the sensor control device 5002 is initially installed inthe sensor applicator 102, the sheath arms 5604 may be received withinthe first detent 5702 a. As discussed below, the sheath 212 may beactuated to move the sheath arms 5604 to the second detent 5702 b, whichplaces the sensor applicator 102 in firing position.

In FIG. 12B, the applicator cap 210 is aligned with the housing 208 andadvanced toward the housing 208 so that the sheath 212 is receivedwithin the applicator cap 210. Instead of rotating the applicator cap210 relative to the housing 208, the threads of the applicator cap 210may be snapped onto the corresponding threads of the housing 208 tocouple the applicator cap 210 to the housing 208. Axial cuts or slots5703 (one shown) defined in the applicator cap 210 may allow portions ofthe applicator cap 210 near its threading to flex outward to be snappedinto engagement with the threading of the housing 208. As the applicatorcap 210 is snapped to the housing 208, the sensor cap 5018 maycorrespondingly be snapped into the cap post 5314.

Similar to the embodiment of FIGS. 11A-11C, the sensor applicator 102may include a sheath locking mechanism configured to ensure that thesheath 212 does not prematurely collapse during a shock event. In theillustrated embodiment, the sheath locking mechanism includes one ormore ribs 5704 (one shown) defined near the base of the sheath 212 andconfigured to interact with one or more ribs 5706 (two shown) and ashoulder 5708 defined near the base of the applicator cap 210. The ribs5704 may be configured to inter-lock between the ribs 5706 and theshoulder 5708 while attaching the applicator cap 210 to the housing 208.More specifically, once the applicator cap 210 is snapped onto thehousing 208, the applicator cap 210 may be rotated (e.g., clockwise),which locates the ribs 5704 of the sheath 212 between the ribs 5706 andthe shoulder 5708 of the applicator cap 210 and thereby “locks” theapplicator cap 210 in place until the user reverse rotates theapplicator cap 210 to remove the applicator cap 210 for use. Engagementof the ribs 5704 between the ribs 5706 and the shoulder 5708 of theapplicator cap 210 may also prevent the sheath 212 from collapsingprematurely.

In FIG. 12C, the applicator cap 210 is removed from the housing 208. Aswith the embodiment of FIGS. 21A-21C, the applicator cap 210 can beremoved by reverse rotating the applicator cap 210, whichcorrespondingly rotates the cap post 5314 in the same direction andcauses sensor cap 5018 to unthread from the mating member 5016, asgenerally described above. Moreover, detaching the sensor cap 5018 fromthe sensor control device 5002 exposes the distal portions of the sensor5010 and the sharp 5012.

As the applicator cap 210 is unscrewed from the housing 208, the ribs5704 defined on the sheath 212 may slidingly engage the tops of the ribs5706 defined on the applicator cap 210. The tops of the ribs 5706 mayprovide corresponding ramped surfaces that result in an upwarddisplacement of the sheath 212 as the applicator cap 210 is rotated, andmoving the sheath 212 upward causes the sheath arms 5604 to flex out ofengagement with the first detent 5702 a to be received within the seconddetent 5702 b. As the sheath 212 moves to the second detent 5702 b, theradial shoulder 5614 moves out of radial engagement with the carrierarm(s) 5608, which allows the passive spring force of the spring 5612 topush upward on the sharp carrier 5306 and force the carrier arm(s) 5608out of engagement with the groove(s) 5610. As the sharp carrier 5306moves upward within the housing 208, the mating member 5016 maycorrespondingly retract until it becomes flush, substantially flush, orsub-flush with the bottom of the sensor control device 5002. At thispoint, the sensor applicator 102 in firing position. Accordingly, inthis embodiment, removing the applicator cap 210 correspondingly causesthe mating member 5016 to retract.

I. Exemplary Firing Mechanism of One-Piece and Two-Piece Applicators

FIGS. 13A-13F illustrate example details of embodiments of the internaldevice mechanics of “firing” the applicator 216 to apply sensor controldevice 222 to a user and including retracting sharp 1030 safely backinto used applicator 216. All together, these drawings represent anexample sequence of driving sharp 1030 (supporting a sensor coupled tosensor control device 222) into the skin of a user, withdrawing thesharp while leaving the sensor behind in operative contact withinterstitial fluid of the user, and adhering the sensor control deviceto the skin of the user with an adhesive. Modification of such activityfor use with the alternative applicator assembly embodiments andcomponents can be appreciated in reference to the same by those withskill in the art. Moreover, applicator 216 may be a sensor applicatorhaving one-piece architecture or a two-piece architecture as disclosedherein.

Turning now to FIG. 13A, a sensor 1102 is supported within sharp 1030,just above the skin 1104 of the user. Rails 1106 (optionally three ofthem) of an upper guide section 1108 may be provided to controlapplicator 216 motion relative to sheath 318. The sheath 318 is held bydetent features 1110 within the applicator 216 such that appropriatedownward force along the longitudinal axis of the applicator 216 willcause the resistance provided by the detent features 1110 to be overcomeso that sharp 1030 and sensor control device 222 can translate along thelongitudinal axis into (and onto) skin 1104 of the user. In addition,catch arms 1112 of sensor carrier 1022 engage the sharp retractionassembly 1024 to maintain the sharp 1030 in a position relative to thesensor control device 222.

In FIG. 13B, user force is applied to overcome or override detentfeatures 1110 and sheath 318 collapses into housing 314 driving thesensor control device 222 (with associated parts) to translate down asindicated by the arrow L along the longitudinal axis. An inner diameterof the upper guide section 1108 of the sheath 318 constrains theposition of carrier arms 1112 through the full stroke of thesensor/sharp insertion process. The retention of the stop surfaces 1114of carrier arms 1112 against the complimentary faces 1116 of the sharpretraction assembly 1024 maintains the position of the members withreturn spring 1118 fully energized. According to embodiments, ratherthan employing user force to drive the sensor control device 222 totranslate down as indicated by the arrow L along the longitudinal axis,housing 314 can include a button (for example, not limitation, a pushbutton) which activates a drive spring (for example, not limitation, acoil spring) to drive the sensor control device 222.

In FIG. 13C, sensor 1102 and sharp 1030 have reached full insertiondepth. In so doing, the carrier arms 1112 clear the upper guide section1108 inner diameter. Then, the compressed force of the coil returnspring 1118 drives angled stop surfaces 1114 radially outward, releasingforce to drive the sharp carrier 1102 of the sharp retraction assembly1024 to pull the (slotted or otherwise configured) sharp 1030 out of theuser and off of the sensor 1102 as indicated by the arrow R in FIG. 13D.

With the sharp 1030 fully retracted as shown in FIG. 13E, the upperguide section 1108 of the sheath 318 is set with a final locking feature1120. As shown in FIG. 13F, the spent applicator assembly 216 is removedfrom the insertion site, leaving behind the sensor control device 222,and with the sharp 1030 secured safely inside the applicator assembly216. The spent applicator assembly 216 is now ready for disposal.

Operation of the applicator 216 when applying the sensor control device222 is designed to provide the user with a sensation that both theinsertion and retraction of the sharp 1030 is performed automatically bythe internal mechanisms of the applicator 216. In other words, thepresent invention avoids the user experiencing the sensation that he ismanually driving the sharp 1030 into his skin. Thus, once the userapplies sufficient force to overcome the resistance from the detentfeatures of the applicator 216, the resulting actions of the applicator216 are perceived to be an automated response to the applicator being“triggered.” The user does not perceive that he is supplying additionalforce to drive the sharp 1030 to pierce his skin despite that all thedriving force is provided by the user and no additional biasing/drivingmeans are used to insert the sharp 1030. As detailed above in FIG. 13C,the retraction of the sharp 1030 is automated by the coil return spring1118 of the applicator 216.

With respect to any of the applicator embodiments described herein, aswell as any of the components thereof, including but not limited to thesharp, sharp module and sensor module embodiments, those of skill in theart will understand that said embodiments can be dimensioned andconfigured for use with sensors configured to sense an analyte level ina bodily fluid in the epidermis, dermis, or subcutaneous tissue of asubject. In some embodiments, for example, sharps and distal portions ofanalyte sensors disclosed herein can both be dimensioned and configuredto be positioned at a particular end-depth (i.e., the furthest point ofpenetration in a tissue or layer of the subject's body, e.g., in theepidermis, dermis, or subcutaneous tissue). With respect to someapplicator embodiments, those of skill in the art will appreciate thatcertain embodiments of sharps can be dimensioned and configured to bepositioned at a different end-depth in the subject's body relative tothe final end-depth of the analyte sensor. In some embodiments, forexample, a sharp can be positioned at a first end-depth in the subject'sepidermis prior to retraction, while a distal portion of an analytesensor can be positioned at a second end-depth in the subject's dermis.In other embodiments, a sharp can be positioned at a first end-depth inthe subject's dermis prior to retraction, while a distal portion of ananalyte sensor can be positioned at a second end-depth in the subject'ssubcutaneous tissue. In still other embodiments, a sharp can bepositioned at a first end-depth prior to retraction and the analytesensor can be positioned at a second end-depth, wherein the firstend-depth and second end-depths are both in the same layer or tissue ofthe subject's body.

Additionally, with respect to any of the applicator embodimentsdescribed herein, those of skill in the art will understand that ananalyte sensor, as well as one or more structural components coupledthereto, including but not limited to one or more spring-mechanisms, canbe disposed within the applicator in an off-center position relative toone or more axes of the applicator. In some applicator embodiments, forexample, an analyte sensor and a spring mechanism can be disposed in afirst off-center position relative to an axis of the applicator on afirst side of the applicator, and the sensor electronics can be disposedin a second off-center position relative to the axis of the applicatoron a second side of the applicator. In other applicator embodiments, theanalyte sensor, spring mechanism, and sensor electronics can be disposedin an off-center position relative to an axis of the applicator on thesame side. Those of skill in the art will appreciate that otherpermutations and configurations in which any or all of the analytesensor, spring mechanism, sensor electronics, and other components ofthe applicator are disposed in a centered or off-centered positionrelative to one or more axes of the applicator are possible and fullywithin the scope of the present disclosure.

Additional details of suitable devices, systems, methods, components andthe operation thereof along with related features are set forth inInternational Publication No. WO2018/136898 to Rao et al., InternationalPublication No. WO2019/236850 to Thomas et al., InternationalPublication No. WO2019/236859 to Thomas et al., InternationalPublication No. WO2019/236876 to Thomas et al., and U.S. PatentPublication No. 2020/0196919, filed Jun. 6, 2019, each of which isincorporated by reference in its entirety herein. Further detailsregarding embodiments of applicators, their components, and variantsthereof, are described in U.S. Patent Publication Nos. 2013/0150691,2016/0331283, and 2018/0235520, all of which are incorporated byreference herein in their entireties and for all purposes. Furtherdetails regarding embodiments of sharp modules, sharps, theircomponents, and variants thereof, are described in U.S. PatentPublication No. 2014/0171771, which is incorporated by reference hereinin its entirety and for all purposes.

J. Exemplary Methods of Calibrating Analyte Sensors

Biochemical sensors can be described by one or more sensingcharacteristics. A common sensing characteristic is referred to as thebiochemical sensor's sensitivity, which is a measure of the sensor'sresponsiveness to the concentration of the chemical or composition it isdesigned to detect. For electrochemical sensors, this response can be inthe form of an electrical current (amperometric) or electrical charge(coulometric). For other types of sensors, the response can be in adifferent form, such as a photonic intensity (e.g., optical light). Thesensitivity of a biochemical analyte sensor can vary depending on anumber of factors, including whether the sensor is in an in vitro stateor an in vivo state.

FIG. 14 is a graph depicting the in vitro sensitivity of an amperometricanalyte sensor. The in vitro sensitivity can be obtained by in vitrotesting the sensor at various analyte concentrations and then performinga regression (e.g., linear or non-linear) or other curve fitting on theresulting data. In this example, the analyte sensor's sensitivity islinear, or substantially linear, and can be modeled according to theequation y=mx+b, where y is the sensor's electrical output current, x isthe analyte level (or concentration), m is the slope of the sensitivityand b is the intercept of the sensitivity, where the intercept generallycorresponds to a background signal (e.g., noise). For sensors with alinear or substantially linear response, the analyte level thatcorresponds to a given current can be determined from the slope andintercept of the sensitivity. Sensors with a non-linear sensitivityrequire additional information to determine the analyte level resultingfrom the sensor's output current, and those of ordinary skill in the artare familiar with manners by which to model non-linear sensitivities. Incertain embodiments of in vivo sensors, the in vitro sensitivity can bethe same as the in vivo sensitivity, but in other embodiments a transfer(or conversion) function is used to translate the in vitro sensitivityinto the in vivo sensitivity that is applicable to the sensor's intendedin vivo use.

Calibration is a technique for improving or maintaining accuracy byadjusting a sensor's measured output to reduce the differences with thesensor's expected output. One or more parameters that describe thesensor's sensing characteristics, like its sensitivity, are establishedfor use in the calibration adjustment.

Certain in vivo analyte monitoring systems require calibration to occurafter implantation of the sensor into the user or patient, either byuser interaction or by the system itself in an automated fashion. Forexample, when user interaction is required, the user performs an invitro measurement (e.g., a blood glucose (BG) measurement using a fingerstick and an in vitro test strip) and enters this into the system, whilethe analyte sensor is implanted. The system then compares the in vitromeasurement with the in vivo signal and, using the differential,determines an estimate of the sensor's in vivo sensitivity. The in vivosensitivity can then be used in an algorithmic process to transform thedata collected with the sensor to a value that indicates the user'sanalyte level. This and other processes that require user action toperform calibration are referred to as “user calibration.” Systems canrequire user calibration due to instability of the sensor's sensitivity,such that the sensitivity drifts or changes over time. Thus, multipleuser calibrations (e.g., according to a periodic (e.g., daily) schedule,variable schedule, or on an as-needed basis) can be required to maintainaccuracy. While the embodiments described herein can incorporate adegree of user calibration for a particular implementation, generallythis is not preferred as it requires the user to perform a painful orotherwise burdensome BG measurement, and can introduce user error.

Some in vivo analyte monitoring systems can regularly adjust thecalibration parameters through the use of automated measurements ofcharacteristics of the sensor made by the system itself (e.g.,processing circuitry executing software). The repeated adjustment of thesensor's sensitivity based on a variable measured by the system (and notthe user) is referred to generally as “system” (or automated)calibration, and can be performed with user calibration, such as anearly BG measurement, or without user calibration. Like the case withrepeated user calibrations, repeated system calibrations are typicallynecessitated by drift in the sensor's sensitivity over time. Thus, whilethe embodiments described herein can be used with a degree of automatedsystem calibration, preferably the sensor's sensitivity is relativelystable over time such that post-implantation calibration is notrequired.

Some in vivo analyte monitoring systems operate with a sensor that isfactory calibrated. Factory calibration refers to the determination orestimation of the one or more calibration parameters prior todistribution to the user or healthcare professional (HCP). Thecalibration parameter can be determined by the sensor manufacturer (orthe manufacturer of the other components of the sensor control device ifthe two entities are different). Many in vivo sensor manufacturingprocesses fabricate the sensors in groups or batches referred to asproduction lots, manufacturing stage lots, or simply lots. A single lotcan include thousands of sensors.

Sensors can include a calibration code or parameter which can be derivedor determined during one or more sensor manufacturing processes andcoded or programmed, as part of the manufacturing process, in the dataprocessing device of the analyte monitoring system or provided on thesensor itself, for example, as a bar code, a laser tag, an RFID tag, orother machine readable information provided on the sensor. Usercalibration during in vivo use of the sensor can be obviated, or thefrequency of in vivo calibrations during sensor wear can be reduced ifthe code is provided to a receiver (or other data processing device). Inembodiments where the calibration code or parameter is provided on thesensor itself, prior to or at the start of the sensor use, thecalibration code or parameter can be automatically transmitted orprovided to the data processing device in the analyte monitoring system.

Some in vivo analyte monitoring system operate with a sensor that can beone or more of factory calibrated, system calibrated, and/or usercalibrated. For example, the sensor can be provided with a calibrationcode or parameter which can allow for factory calibration. If theinformation is provided to a receiver (for example, entered by a user),the sensor can operate as a factory calibrated sensor. If theinformation is not provided to a receiver, the sensor can operate as auser calibrated sensor and/or a system calibrated sensor.

In a further aspect, programming or executable instructions can beprovided or stored in the data processing device of the analytemonitoring system, and/or the receiver/controller unit, to provide atime varying adjustment algorithm to the in vivo sensor during use. Forexample, based on a retrospective statistical analysis of analytesensors used in vivo and the corresponding glucose level feedback, apredetermined or analytical curve or a database can be generated whichis time based, and configured to provide additional adjustment to theone or more in vivo sensor parameters to compensate for potential sensordrift in stability profile, or other factors.

In accordance with the disclosed subject matter, the analyte monitoringsystem can be configured to compensate or adjust for the sensorsensitivity based on a sensor drift profile. A time varying parameterβ(t) can be defined or determined based on analysis of sensor behaviorduring in vivo use, and a time varying drift profile can be determined.In certain aspects, the compensation or adjustment to the sensorsensitivity can be programmed in the receiver unit, the controller ordata processor of the analyte monitoring system such that thecompensation or the adjustment or both can be performed automaticallyand/or iteratively when sensor data is received from the analyte sensor.In accordance with the disclosed subject matter, the adjustment orcompensation algorithm can be initiated or executed by the user (ratherthan self-initiating or executing) such that the adjustment or thecompensation to the analyte sensor sensitivity profile is performed orexecuted upon user initiation or activation of the correspondingfunction or routine, or upon the user entering the sensor calibrationcode.

In accordance with the disclosed subject matter, each sensor in thesensor lot (in some instances not including sample sensors used for invitro testing) can be examined non-destructively to determine or measureits characteristics such as membrane thickness at one or more points ofthe sensor, and other characteristics including physical characteristicssuch as the surface area/volume of the active area can be measured ordetermined. Such measurement or determination can be performed in anautomated manner using, for example, optical scanners or other suitablemeasurement devices or systems, and the determined sensorcharacteristics for each sensor in the sensor lot is compared to thecorresponding mean values based on the sample sensors for possiblecorrection of the calibration parameter or code assigned to each sensor.For example, for a calibration parameter defined as the sensorsensitivity, the sensitivity is approximately inversely proportional tothe membrane thickness, such that, for example, a sensor having ameasured membrane thickness of approximately 4% greater than the meanmembrane thickness for the sampled sensors from the same sensor lot asthe sensor, the sensitivity assigned to that sensor in one embodiment isthe mean sensitivity determined from the sampled sensors divided by1.04. Likewise, since the sensitivity is approximately proportional toactive area of the sensor, a sensor having measured active area ofapproximately 3% lower than the mean active area for the sampled sensorsfrom the same sensor lot, the sensitivity assigned to that sensor is themean sensitivity multiplied by 0.97. The assigned sensitivity can bedetermined from the mean sensitivity from the sampled sensors, bymultiple successive adjustments for each examination or measurement ofthe sensor. In certain embodiments, examination or measurement of eachsensor can additionally include measurement of membrane consistency ortexture in addition to the membrane thickness and/or surface are orvolume of the active sensing area.

Additional information regarding sensor calibration is provided in U.S.Publication No. 2010/00230285 and U.S. Publication No. 2019/0274598,each of which is incorporated by reference herein in its entirety.

K. Exemplary Bluetooth Communication Protocols

The storage memory 5030 of the sensor 110 can include the softwareblocks related to communication protocols of the communication module.For example, the storage memory 5030 can include a BLE services softwareblock with functions to provide interfaces to make the BLE module 5041available to the computing hardware of the sensor 110. These softwarefunctions can include a BLE logical interface and interface parser. BLEservices offered by the communication module 5040 can include thegeneric access profile service, the generic attribute service, genericaccess service, device information service, data transmission services,and security services. The data transmission service can be a primaryservice used for transmitting data such as sensor control data, sensorstatus data, analyte measurement data (historical and current), andevent log data. The sensor status data can include error data, currenttime active, and software state. The analyte measurement data caninclude information such as current and historical raw measurementvalues, current and historical values after processing using anappropriate algorithm or model, projections and trends of measurementlevels, comparisons of other values to patient-specific averages, callsto action as determined by the algorithms or models and other similartypes of data.

According to aspects of the disclosed subject matter, and as embodiedherein, a sensor 110 can be configured to communicate with multipledevices concurrently by adapting the features of a communicationprotocol or medium supported by the hardware and radios of the sensor110. As an example, the BLE module 5041 of the communication module 5040can be provided with software or firmware to enable multiple concurrentconnections between the sensor 110 as a central device and the otherdevices as peripheral devices, or as a peripheral device where anotherdevice is a central device.

Connections, and ensuing communication sessions, between two devicesusing a communication protocol such as BLE can be characterized by asimilar physical channel operated between the two devices (e.g., asensor 110 and data receiving device 120). The physical channel caninclude a single channel or a series of channels, including for exampleand without limitation using an agreed upon series of channelsdetermined by a common clock and channel- or frequency-hopping sequence.Communication sessions can use a similar amount of the availablecommunication spectrum, and multiple such communication sessions canexist in proximity. In certain embodiment, each collection of devices ina communication session uses a different physical channel or series ofchannels, to manage interference of devices in the same proximity.

For purpose of illustration and not limitation, reference is made to anexemplary embodiment of a procedure for a sensor-receiver connection foruse with the disclosed subject matter. First, the sensor 110 repeatedlyadvertises its connection information to its environment in a search fora data receiving device 120. The sensor 110 can repeat advertising on aregular basis until a connection established. The data receiving device120 detects the advertising packet and scans and filters for the sensor120 to connect to through the data provided in the advertising packet.Next, data receiving device 120 sends a scan request command and thesensor 110 responds with a scan response packet providing additionaldetails. Then, the data receiving device 120 sends a connection requestusing the Bluetooth device address associated with the data receivingdevice 120. The data receiving device 120 can also continuously requestto establish a connection to a sensor 110 with a specific Bluetoothdevice address. Then, the devices establish an initial connectionallowing them to begin to exchange data. The devices begin a process toinitialize data exchange services and perform a mutual authenticationprocedure.

During a first connection between the sensor 110 and data receivingdevice 120, the data receiving device 120 can initialize a service,characteristic, and attribute discovery procedure. The data receivingdevice 120 can evaluate these features of the sensor 110 and store themfor use during subsequent connections. Next, the devices enable anotification for a customized security service used for mutualauthentication of the sensor 110 and data receiving device 120. Themutual authentication procedure can be automated and require no userinteraction. Following the successful completion of the mutualauthentication procedure, the sensor 110 sends a connection parameterupdate to request the data receiving device 120 to use connectionparameter settings preferred by the sensor 110 and configured to maximumlongevity.

The data receiving device 120 then performs sensor control procedures tobackfill historical data, current data, event log, and factory data. Asan example, for each type of data, the data receiving device 120 sends arequest to initiate a backfill process. The request can specify a rangeof records defined based on, for example, the measurement value,timestamp, or similar, as appropriate. The sensor 110 responds withrequested data until all previously unsent data in the memory of thesensor 110 is delivered to the data receiving device 120. The sensor 110can respond to a backfill request from the data receiving device 120that all data has already been sent. Once backfill is completed, thedata receiving device 120 can notify sensor 110 that it is ready toreceive regular measurement readings. The sensor 110 can send readingsacross multiple notifications result on a repeating basis. As embodiedherein, the multiple notifications can be redundant notifications toensure that data is transmitted correctly. Alternatively, multiplenotifications can make up a single payload.

For purpose of illustration and not limitation, reference is made to anexemplary embodiment of a procedure to send a shutdown command to thesensor 110. The shutdown operation is executed if the sensor 110 is in,for example, an error state, insertion failed state, or sensor expiredstate. If the sensor 110 is not in those states, the sensor 110 can logthe command and execute the shutdown when sensor 110 transitions intothe error state or sensor expired state. The data receiving device 120sends a properly formatted shutdown command to the sensor 110. If thesensor 110 is actively processing another command, the sensor 110 willrespond with a standard error response indicating that the sensor 110 isbusy. Otherwise, the sensor 110 sends a response as the command isreceived. Additionally, the sensor 110 sends a success notificationthrough the sensor control characteristic to acknowledge the sensor 110has received the command. The sensor 110 registers the shutdown command.At the next appropriate opportunity (e.g., depending on the currentsensor state, as described herein), the sensor 110 will shut down.

L. Exemplary Sensor States and Activation

For purpose of illustration and not limitation, reference is made to theexemplary embodiment of a high-level depiction of a state machinerepresentation 6000 of the actions that can be taken by the sensor 110as shown in FIG. 15. After initialization, the sensor enters state 6005,which relates to the manufacture of the sensor 110. In the manufacturestate 6005 the sensor 110 can be configured for operation, for example,the storage memory 5030 can be written. At various times while in state6005, the sensor 110 checks for a received command to go to the storagestate 6015. Upon entry to the storage state 6015, the sensor performs asoftware integrity check. While in the storage state 6015, the sensorcan also receive an activation request command before advancing to theinsertion detection state 6025.

Upon entry to state 6025, the sensor 110 can store information relatingto devices authenticated to communicate with the sensor as set duringactivation or initialize algorithms related to conducting andinterpreting measurements from the sensing hardware 5060. The sensor 110can also initialize a lifecycle timer, responsible for maintaining anactive count of the time of operation of the sensor 110 and begincommunication with authenticated devices to transmit recorded data.While in the insertion detection state 6025, the sensor can enter state6030, where the sensor 110 checks whether the time of operation is equalto a predetermined threshold. This time of operation threshold cancorrespond to a timeout function for determining whether an insertionhas been successful. If the time of operation has reached the threshold,the sensor 110 advances to state 6035, in which the sensor 110 checkswhether the average data reading is greater than a threshold amountcorresponding to an expected data reading volume for triggeringdetection of a successful insertion. If the data reading volume is lowerthan the threshold while in state 6035, the sensor advances to state6040, corresponding to a failed insertion. If the data reading volumesatisfies the threshold, the sensor advances to the active paired state6055.

The active paired state 6055 of the sensor 110 reflects the state whilethe sensor 110 is operating as normal by recording measurements,processing the measurements, and reporting them as appropriate. While inthe active paired state 6055, the sensor 110 sends measurement resultsor attempts to establish a connection with a receiving device 120. Thesensor 110 also increments the time of operation. Once the sensor 110reaches a predetermined threshold time of operation (e.g., once the timeof operation reaches a predetermined threshold), the sensor 110transitions to the active expired state 6065. The active expired state6065 of the sensor 110 reflects the state while the sensor 110 hasoperated for its maximum predetermined amount of time.

While in the active expired state 6065, the sensor 110 can generallyperform operations relating to winding down operation and ensuring thatthe collected measurements have been securely transmitted to receivingdevices as needed. For example, while in the active expired state 6065,the sensor 110 can transmit collected data and, if no connection isavailable, can increase efforts to discover authenticated devices nearbyand establish and connection therewith. While in the active expiredstate 6065, the sensor 110 can receive a shutdown command at state 6070.If no shutdown command is received, the sensor 110 can also, at state6075, check if the time of operation has exceeded a final operationthreshold. The final operation threshold can be based on the batterylife of the sensor 110. The normal termination state 6080 corresponds tothe final operations of the sensor 110 and ultimately shutting down thesensor 110.

Before a sensor is activated, the ASIC 5000 resides in a low powerstorage mode state. The activation process can begin, for example, whenan incoming RF field (e.g., NFC field) drives the voltage of the powersupply to the ASIC 5000 above a reset threshold, which causes the sensor110 to enter a wake-up state. While in the wake-up state, the ASIC 5000enters an activation sequence state. The ASIC 5000 then wakes thecommunication module 5040. The communication module 5040 is initialized,triggering a power on self-test. The power on self-test can include theASIC 5000 communicating with the communication module 5040 using aprescribed sequence of reading and writing data to verify the memory andone-time programmable memory are not corrupted.

When the ASIC 5000 enters the measurement mode for the first time, aninsertion detection sequence is performed to verify that the sensor 110has been properly installed onto the patient's body before a propermeasurement can take place. First, the sensor 110 interprets a commandto activate the measurement configuration process, causing the ASIC 5000to enter measurement command mode. The sensor 110 then temporarilyenters the measurement lifecycle state to run a number of consecutivemeasurements to test whether the insertion has been successful. Thecommunication module 5040 or ASIC 5000 evaluates the measurement resultsto determine insertion success. When insertion is deemed successful, thesensor 110 enters a measurement state, in which the sensor 110 beginstaking regular measurements using sensing hardware 5060. If the sensor110 determines that the insertion was not successful, sensor 110 istriggered into an insertion failure mode, in which the ASIC 5000 iscommanded back to storage mode while the communication module 5040disables itself.

M. Exemplary Over-the-Air Updates

FIG. 1B further illustrates an example operating environment forproviding over-the-air (“OTA”) updates for use with the techniquesdescribed herein. An operator of the analyte monitoring system 100 canbundle updates for the data receiving device 120 or sensor 110 intoupdates for an application executing on the multi-purpose data receivingdevice 130. Using available communication channels between the datareceiving device 120, the multi-purpose data receiving device 130, andthe sensor 110, the multi-purpose data receiving device 130 can receiveregular updates for the data receiving device 120 or sensor 110 andinitiate installation of the updates on the data receiving device 120 orsensor 110. The multi-purpose data receiving device 130 acts as aninstallation or update platform for the data receiving device 120 orsensor 110 because the application that enables the multi-purpose datareceiving device 130 to communicate with an analyte sensor 110, datareceiving device 120 and/or remote application server 150 can updatesoftware or firmware on a data receiving device 120 or sensor 110without wide-area networking capabilities.

As embodied herein, a remote application server 150 operated by themanufacturer of the analyte sensor 110 and/or the operator of theanalyte monitoring system 100 can provide software and firmware updatesto the devices of the analyte monitoring system 100. In particularembodiments, the remote application server 150 can provides the updatedsoftware and firmware to a user device 140 or directly to amulti-purpose data receiving device. As embodied herein, the remoteapplication server 150 can also provide application software updates toan application storefront server 160 using interfaces provided by theapplication storefront. The multi-purpose data receiving device 130 cancontact the application storefront server 160 periodically to downloadand install the updates.

After the multi-purpose data receiving device 130 downloads anapplication update including a firmware or software update for a datareceiving device 120 or sensor 110, the data receiving device 120 orsensor 110 and multi-purpose data receiving device 130 establish aconnection. The multi-purpose data receiving device 130 determines thata firmware or software update is available for the data receiving device120 or sensor 110. The multi-purpose data receiving device 130 canprepare the software or firmware update for delivery to the datareceiving device 120 or sensor 110. As an example, the multi-purposedata receiving device 130 can compress or segment the data associatedwith the software or firmware update, can encrypt or decrypt thefirmware or software update, or can perform an integrity check of thefirmware or software update. The multi-purpose data receiving device 130sends the data for the firmware or software update to the data receivingdevice 120 or sensor 110. The multi-purpose data receiving device 130can also send a command to the data receiving device 120 or sensor 110to initiate the update. Additionally or alternatively, the multi-purposedata receiving device 130 can provide a notification to the user of themulti-purpose data receiving device 130 and include instructions forfacilitating the update, such as instructions to keep the data receivingdevice 120 and the multi-purpose data receiving device 130 connected toa power source and in close proximity until the update is complete.

The data receiving device 120 or sensor 110 receives the data for theupdate and the command to initiate the update from the multi-purposedata receiving device 130. The data receiving device 120 can theninstall the firmware or software update. To install the update, the datareceiving device 120 or sensor 110 can place or restart itself in aso-called “safe” mode with limited operational capabilities. Once theupdate is completed, the data receiving device 120 or sensor 110re-enters or resets into a standard operational mode. The data receivingdevice 120 or sensor 110 can perform one or more self-tests to determinethat the firmware or software update was installed successfully. Themulti-purpose data receiving device 130 can receive the notification ofthe successful update. The multi-purpose data receiving device 130 canthen report a confirmation of the successful update to the remoteapplication server 150.

In particular embodiments, the storage memory 5030 of the sensor 110includes one-time programmable (OTP) memory. The term OTP memory canrefer to memory that includes access restrictions and security tofacilitate writing to particular addresses or segments in the memory apredetermined number of times. The memory 5030 can be prearranged intomultiple pre-allocated memory blocks or containers. The containers arepre-allocated into a fixed size. If storage memory 5030 is one-timeprogramming memory, the containers can be considered to be in anon-programmable state. Additional containers which have not yet beenwritten to can be placed into a programmable or writable state.Containerizing the storage memory 5030 in this fashion can improve thetransportability of code and data to be written to the storage memory5030. Updating the software of a device (e.g., the sensor devicedescribed herein) stored in an OTP memory can be performed bysuperseding only the code in a particular previously-written containeror containers with updated code written to a new container orcontainers, rather than replacing the entire code in the memory. In asecond embodiment, the memory is not prearranged. Instead, the spaceallocated for data is dynamically allocated or determined as needed.Incremental updates can be issued, as containers of varying sizes can bedefined where updates are anticipated.

FIG. 16 is a diagram illustrating an example operational and data flowfor over-the-air (OTA) programming of a storage memory 5030 in a sensordevice 100 as well as use of the memory after the OTA programming inexecution of processes by the sensor device 110 according to thedisclosed subject matter. In the example OTA programming 500 illustratedin FIG. 5, a request is sent from an external device (e.g., the datareceiving device 130) to initiate OTA programming (or re-programming).At 511, a communication module 5040 of a sensor device 110 receives anOTA programming command. The communication module 5040 sends the OTAprogramming command to the microcontroller 5010 of the sensor device110.

At 531, after receiving the OTA programming command, the microcontroller5010 validates the OTA programming command. The microcontroller 5010 candetermine, for example, whether the OTA programming command is signedwith an appropriate digital signature token. Upon determining that theOTA programming command is valid, the microcontroller 5010 can set thesensor device into an OTA programming mode. At 532, the microcontroller5010 can validate the OTA programming data. At 533, The microcontroller5010 can reset the sensor device 110 to re-initialize the sensor device110 in a programming state. Once the sensor device 110 has transitionedinto the OTA programming state, the microcontroller 5010 can begin towrite data to the rewriteable memory 540 (e.g., memory 5020) of thesensor device at 534 and write data to the OTP memory 550 of the sensordevice at 535 (e.g., storage memory 5030). The data written by themicrocontroller 5010 can be based on the validated OTA programming data.The microcontroller 5010 can write data to cause one or more programmingblocks or regions of the OTP memory 550 to be marked invalid orinaccessible. The data written to the free or unused portion of the OTPmemory can be used to replace invalidated or inaccessible programmingblocks of the OTP memory 550. After the microcontroller 5010 writes thedata to the respective memories at 534 and 535, the microcontroller 5010can perform one or more software integrity checks to ensure that errorswere not introduced into the programming blocks during the writingprocess. Once the microcontroller 5010 is able to determine that thedata has been written without errors, the microcontroller 5010 canresume standard operations of the sensor device.

In execution mode, at 536, the microcontroller 5010 can retrieve aprogramming manifest or profile from the rewriteable memory 540. Theprogramming manifest or profile can include a listing of the validsoftware programming blocks and can include a guide to program executionfor the sensor 110. By following the programming manifest or profile,the microcontroller 5010 can determine which memory blocks of the OTPmemory 550 are appropriate to execute and avoid execution of out-of-dateor invalidated programming blocks or reference to out-of-date data. At537, the microcontroller 5010 can selectively retrieve memory blocksfrom the OTP memory 550. At 538, the microcontroller 5010 can use theretrieved memory blocks, by executing programming code stored or usingvariable stored in the memory.

N. Exemplary Security and Other Architecture Features

As embodied herein a first layer of security for communications betweenthe analyte sensor 110 and other devices can be established based onsecurity protocols specified by and integrated in the communicationprotocols used for the communication. Another layer of security can bebased on communication protocols that necessitate close proximity ofcommunicating devices. Furthermore certain packets and/or certain dataincluded within packets can be encrypted while other packets and/or datawithin packets is otherwise encrypted or not encrypted. Additionally oralternatively, application layer encryption can be used with one or moreblock ciphers or stream ciphers to establish mutual authentication andcommunication encryption with other devices in the analyte monitoringsystem 100.

The ASIC 5000 of the analyte sensor 110 can be configured to dynamicallygenerate authentication and encryption keys using data retained withinthe storage memory 5030. The storage memory 5030 can also bepre-programmed with a set of valid authentication and encryption keys touse with particular classes of devices. The ASIC 5000 can be furtherconfigured to perform authentication procedures with other devices usingreceived data and apply the generated key to sensitive data prior totransmitting the sensitive data. The generated key can be unique to theanalyte sensor 110, unique to a pair of devices, unique to acommunication session between an analyte sensor 110 and other device,unique to a message sent during a communication session, or unique to ablock of data contained within a message.

Both the sensor 110 and a data receiving device 120 can ensure theauthorization of the other party in a communication session to, forexample, issue a command or receive data. In particular embodiments,identity authentication can be performed through two features. First,the party asserting its identity provides a validated certificate signedby the manufacturer of the device or the operator of the analytemonitoring system 100. Second, authentication can be enforced throughthe use of public keys and private keys, and shared secrets derivedtherefrom, established by the devices of the analyte monitoring system100 or established by the operator of the analyte monitoring system 100.To confirm the identity of the other party, the party can provide proofthat the party has control of its private key.

The manufacturer of the analyte sensor 110, data receiving device 120,or provider of the application for multi-purpose data receiving device130 can provide information and programming necessary for the devices tosecurely communicate through secured programming and updates. Forexample, the manufacturer can provide information that can be used togenerate encryption keys for each device, including secured root keysfor the analyte sensor 110 and optionally for the data receiving device120 that can be used in combination with device-specific information andoperational data (e.g., entropy-based random values) to generateencryption values unique to the device, session, or data transmission asneed.

Analyte data associated with a user is sensitive data at least in partbecause this information can be used for a variety of purposes,including for health monitoring and medication dosing decisions. Inaddition to user data, the analyte monitoring system 100 can enforcesecurity hardening against efforts by outside parties toreverse-engineering. Communication connections can be encrypted using adevice-unique or session-unique encryption key. Encrypted communicationsor unencrypted communications between any two devices can be verifiedwith transmission integrity checks built into the communications.Analyte sensor 110 operations can be protected from tampering byrestricting access to read and write functions to the memory 5020 via acommunication interface. The sensor can be configured to grant accessonly to known or “trusted” devices, provided in a “whitelist” or only todevices that can provide a predetermined code associated with themanufacturer or an otherwise authenticated user. A whitelist canrepresent an exclusive range, meaning that no connection identifiersbesides those included in the whitelist will be used, or a preferredrange, in which the whitelist is searched first, but other devices canstill be used. The sensor 110 can further deny and shut down connectionrequests if the requestor cannot complete a login procedure over acommunication interface within a predetermined period of time (e.g.,within four seconds). These characteristics safeguard against specificdenial of service attacks, and in particular against denial of serviceattacks on a BLE interface.

As embodied herein, the analyte monitoring system 100 can employperiodic key rotation to further reduce the likelihood of key compromiseand exploitation. A key rotation strategy employed by the analytemonitoring system 100 can be designed to support backward compatibilityof field-deployed or distributed devices. As an example, the analytemonitoring system 100 can employ keys for downstream devices (e.g.,devices that are in the field or cannot be feasibly provided updates)that are designed to be compatible with multiple generations of keysused by upstream devices.

For purpose of illustration and not limitation, reference is made to theexemplary embodiment of a message sequence diagram 600 for use with thedisclosed subject matter as shown in FIG. 17 and demonstrating anexample exchange of data between a pair of devices, particularly asensor 110 and a data receiving device 120. The data receiving device120 can, as embodied herein, be a data receiving device 120 or amulti-purpose data receiving device 130. At step 605, the data receivingdevice 120 can transmit a sensor activation command 605 to the sensor110, for example via a short-range communication protocol. The sensor110 can, prior to step 605 be in a primarily dormant state, preservingits battery until full activation is needed. After activation duringstep 610, the sensor 110 can collect data or perform other operations asappropriate to the sensing hardware 5060 of the sensor 110. At step 615the data receiving device 120 can initiate an authentication requestcommand 615. In response to the authentication request command 615, boththe sensor 110 and data receiving device 120 can engage in a mutualauthentication process 620. The mutual authentication process 620 caninvolve the transfer of data, including challenge parameters that allowthe sensor 110 and data receiving device 120 to ensure that the otherdevice is sufficiently capable of adhering to an agreed-upon securityframework described herein. Mutual authentication can be based onmechanisms for authentication of two or more entities to each other withor without on-line trusted third parties to verify establishment of asecret key via challenge-response. Mutual authentication can beperformed using two-, three-, four-, or five-pass authentication, orsimilar versions thereof.

Following a successful mutual authentication process 620, at step 625the sensor 110 can provide the data receiving device 120 with a sensorsecret 625. The sensor secret can contain sensor-unique values and bederived from random values generated during manufacture. The sensorsecret can be encrypted prior to or during transmission to preventthird-parties from accessing the secret. The sensor secret 625 can beencrypted via one or more of the keys generated by or in response to themutual authentication process 620. At step 630, the data receivingdevice 120 can derive a sensor-unique encryption key from the sensorsecret. The sensor-unique encryption key can further be session-unique.As such, the sensor-unique encryption key can be determined by eachdevice without being transmitted between the sensor 110 or datareceiving device 120. At step 635, the sensor 110 can encrypt data to beincluded in payload. At step 640, the sensor 110 can transmit theencrypted payload 640 to the data receiving device 120 using thecommunication link established between the appropriate communicationmodels of the sensor 110 and data receiving device 120. At step 645, thedata receiving device 120 can decrypt the payload using thesensor-unique encryption key derived during step 630. Following step645, the sensor 110 can deliver additional (including newly collected)data and the data receiving device 120 can process the received dataappropriately.

As discussed herein, the sensor 110 can be a device with restrictedprocessing power, battery supply, and storage. The encryption techniquesused by the sensor 110 (e.g., the cipher algorithm or the choice ofimplementation of the algorithm) can be selected based at least in parton these restrictions. The data receiving device 120 can be a morepowerful device with fewer restrictions of this nature. Therefore, thedata receiving device 120 can employ more sophisticated, computationallyintense encryption techniques, such as cipher algorithms andimplementations.

O. Exemplary Payload/Communication Frequencies

The analyte sensor 110 can be configured to alter its discoverabilitybehavior to attempt to increase the probability of the receiving devicereceiving an appropriate data packet and/or provide an acknowledgementsignal or otherwise reduce restrictions that can be causing an inabilityto receive an acknowledgement signal. Altering the discoverabilitybehavior of the analyte sensor 110 can include, for example and withoutlimitation, altering the frequency at which connection data is includedin a data packet, altering how frequently data packets are transmittedgenerally, lengthening or shortening the broadcast window for datapackets, altering the amount of time that the analyte sensor 110 listensfor acknowledgement or scan signals after broadcasting, includingdirected transmissions to one or more devices (e.g., through one or moreattempted transmissions) that have previously communicated with theanalyte sensor 110 and/or to one or more devices on a whitelist,altering a transmission power associated with the communication modulewhen broadcasting the data packets (e.g., to increase the range of thebroadcast or decrease energy consumed and extend the life of the batteryof the analyte sensor), altering the rate of preparing and broadcastingdata packets, or a combination of one or more other alterations.Additionally, or alternatively, the receiving device can similarlyadjust parameters relating to the listening behavior of the device toincrease the likelihood of receiving a data packet including connectiondata.

As embodied herein, the analyte sensor 110 can be configured tobroadcast data packets using two types of windows. The first windowrefers to the rate at which the analyte sensor 110 is configured tooperate the communication hardware. The second window refers to the rateat which the analyte sensor 110 is configured to be activelytransmitting data packets (e.g., broadcasting). As an example, the firstwindow can indicate that the analyte sensor 110 operates thecommunication hardware to send and/or receive data packets (includingconnection data) during the first 2 seconds of each 60 second period.The second window can indicate that, during each 2 second window, theanalyte sensor 110 transmits a data packet every 60 milliseconds. Therest of the time during the 2 second window, the analyte sensor 110 isscanning. The analyte sensor 110 can lengthen or shorten either windowto modify the discoverability behavior of the analyte sensor 110.

In particular embodiments, the discoverability behavior of the analytesensor can be stored in a discoverability profile, and alterations canbe made based on one or more factors, such as the status of the analytesensor 110 and/or by applying rules based on the status of the analytesensor 110. For example, when the battery level of the analyte sensor110 is below a certain amount, the rules can cause the analyte sensor110 to decrease the power consumed by the broadcast process. As anotherexample, configuration settings associated with broadcasting orotherwise transmitting packets can be adjusted based on the ambienttemperature, the temperature of the analyte sensor 110, or thetemperature of certain components of communication hardware of theanalyte sensor 110. In addition to modifying the transmission power,other parameters associated with the transmission capabilities orprocesses of the communication hardware of the analyte sensor 110 can bemodified, including, but not limited to, transmission rate, frequency,and timing. As another example, when the analyte data indicates that thesubject is, or is about to be, experiencing a negative health event, therules can cause the analyte sensor 110 to increase its discoverabilityto alert the receiving device of the negative health event.

P. Exemplary Sensor Sensitivity Initialization/Adjustment Features

As embodied herein, certain calibration features for the sensinghardware 5060 of the analyte sensor 110 can be adjusted based onexternal or interval environment features as well as to compensate forthe decay of the sensing hardware 5060 during expended period of disuse(e.g., a “shelf time” prior to use). The calibration features of thesensing hardware 5060 can be autonomously adjusted by the sensor 110(e.g., by operation of the ASIC 5000 to modify features in the memory5020 or storage 5030) or can be adjusted by other devices of the analytemonitoring system 100.

As an example, sensor sensitivity of the sensing hardware 5060 can beadjusted based on external temperature data or the time sincemanufacture. When external temperatures are monitored during the storageof the sensors, the disclosed subject matter can adaptively change thecompensation to sensor sensitivity over time when the device experienceschanging storage conditions. For purpose of illustration notlimitations, adaptive sensitivity adjustment can be performed in an“active” storage mode where the analyte sensor 110 wakes up periodicallyto measure temperature. These features can save the battery of theanalyte device and extend the lifespan of the analyte sensors. At eachtemperature measurement, the analyte sensor 110 can calculate asensitivity adjustment for that time period based on the measuredtemperature. Then, the temperature-weighted adjustments can beaccumulated over the active storage mode period to calculate a totalsensor sensitivity adjustment value at the end of the active storagemode (e.g., at insertion). Similarly, at insertion, the sensor 110 candetermine the time difference between manufacture of the sensor 110(which can be written to the storage 5030 of the ASIC 5000) or thesensing hardware 5060 and modify sensor sensitivity or other calibrationfeatures according to one or more known decay rates or formulas.

Additionally, for purpose of illustration and not limitation, asembodied herein, sensor sensitivity adjustments can account for othersensor conditions, such as sensor drift. Sensor sensitivity adjustmentscan be hardcoded into the sensor 110 during manufacture, for example inthe case of sensor drift, based on an estimate of how much an averagesensor would drift. Sensor 110 can use a calibration function that hastime-varying functions for sensor offset and gain, which can account fordrift over a wear period of the sensor. Thus, sensor 110 can utilize afunction used to transform an interstitial current to interstitialglucose utilizing device-dependent functions describing sensor 110 driftover time, and which can represent sensor sensitivity, and can be devicespecific, combined with a baseline of the glucose profile. Suchfunctions to account for sensor sensitivity and drift can improve sensor110 accuracy over a wear period and without involving user calibration.

Q. Exemplary Model-based Analyte Measurements

The sensor 110 detects raw measurement values from sensing hardware5060. On-sensor processing can be performed, such as by one or moremodels trained to interpret the raw measurement values. Models can bemachine learned models trained off-device to detect, predict, orinterpret the raw measurement values to detect, predict, or interpretthe levels of one or more analytes. Additional trained models canoperate on the output of the machine learning models trained to interactwith raw measurement values. As an example, models can be used todetect, predict, or recommend events based on the raw measurements andtype of analyte(s) detected by the sensing hardware 5060. Events caninclude, initiation or completion of physical activity, meals,application of medical treatment or medication, emergent health events,and other events of a similar nature.

Models can be provided to the sensor 110, data receiving device 120, ormulti-purpose data receiving device 130 during manufacture or duringfirmware or software updates. Models can be periodically refined, suchas by the manufacturer of the sensor 110 or the operator of the analytemonitoring system 100, based on data received from the sensor 110 anddata receiving devices of an individual user or multiple userscollectively. In certain embodiments, the sensor 110 includes sufficientcomputational components to assist with further training or refinementof the machine learned models, such as based on unique features of theuser to which the sensor 110 is attached. Machine learning models caninclude, by way of example and not limitation, models trained using orencompassing decision tree analysis, gradient boosting, ada boosting,artificial neural networks or variants thereof, linear discriminantanalysis, nearest neighbor analysis, support vector machines, supervisedor unsupervised classification, and others. The models can also includealgorithmic or rules-based models in addition to machine learned models.Model-based processing can be performed by other devices, including thedata receiving device 120 or multi-purpose data receiving device 130,upon receiving data from the sensor 110 (or other downstream devices).

R. Exemplary Alarm Features

Data transmitted between the sensor 110 and a data receiving device 120can include raw or processed measurement values. Data transmittedbetween the sensor 110 and data receiving device 120 can further includealarms or notification for display to a user. The data receiving device120 can display or otherwise convey notifications to the user based onthe raw or processed measurement values or can display alarms whenreceived from the sensor 110. Alarms that may be triggered for displayto the user include alarms based on direct analyte values (e.g.,one-time reading exceeding a threshold or failing to satisfy athreshold), analyte value trends (e.g., average reading over a setperiod of time exceeding a threshold or failing to satisfy a threshold;slope); analyte value predictions (e.g., algorithmic calculation basedon analyte values exceeds a threshold or fails to satisfy a threshold),sensor alerts (e.g., suspected malfunction detected), communicationalerts (e.g., no communication between sensor 110 and data receivingdevice 120 for a threshold period of time; unknown device attempting orfailing to initiate a communication session with the sensor 110),reminders (e.g., reminder to charge data receiving device 120; reminderto take a medication or perform other activity), and other alerts of asimilar nature. For purpose of illustration and not limitation, asembodied herein, the alarm parameters described herein can beconfigurable by a user or can be fixed during manufacture, orcombinations of user-settable and non-user-settable parameters.

S. Exemplary Electrode Configurations

Sensor configurations featuring a single active area that is configuredfor detection of a corresponding single analyte can employ two-electrodeor three-electrode detection motifs, as described further herein inreference to FIGS. 18A-18C. Sensor configurations featuring twodifferent active areas for detection of separate analytes, either uponseparate working electrodes or upon the same working electrode, aredescribed separately thereafter in reference to FIGS. 19A-21C. Sensorconfigurations having multiple working electrodes can be particularlyadvantageous for incorporating two different active areas within thesame sensor tail, since the signal contribution from each active areacan be determined more readily.

When a single working electrode is present in an analyte sensor,three-electrode sensor configurations can include a working electrode, acounter electrode, and a reference electrode. Related two-electrodesensor configurations can include a working electrode and a secondelectrode, in which the second electrode can function as both a counterelectrode and a reference electrode (i.e., a counter/referenceelectrode). The various electrodes can be at least partially stacked(layered) upon one another and/or laterally spaced apart from oneanother upon the sensor tail. Suitable sensor configurations can besubstantially flat in shape or substantially cylindrical in shape, orany other suitable shape. In any of the sensor configurations disclosedherein, the various electrodes can be electrically isolated from oneanother by a dielectric material or similar insulator.

Analyte sensors featuring multiple working electrodes can similarlyinclude at least one additional electrode. When one additional electrodeis present, the one additional electrode can function as acounter/reference electrode for each of the multiple working electrodes.When two additional electrodes are present, one of the additionalelectrodes can function as a counter electrode for each of the multipleworking electrodes and the other of the additional electrodes canfunction as a reference electrode for each of the multiple workingelectrodes.

FIG. 18A shows a diagram of an illustrative two-electrode analyte sensorconfiguration, which is compatible for use in the disclosure herein. Asshown, analyte sensor 200 includes substrate 30212 disposed betweenworking electrode 214 and counter/reference electrode 30216.Alternately, working electrode 214 and counter/reference electrode 30216can be located upon the same side of substrate 30212 with a dielectricmaterial interposed in between (configuration not shown). Active area218 is disposed as at least one layer upon at least a portion of workingelectrode 214. Active area 218 can include multiple spots or a singlespot configured for detection of an analyte, as discussed furtherherein.

Referring still to FIG. 18A, membrane 220 overcoats at least active area218. In certain embodiments, membrane 220 can also overcoat some or allof working electrode 214 and/or counter/reference electrode 30216, orthe entirety of analyte sensor 200. One or both faces of analyte sensor200 can be overcoated with membrane 220. Membrane 220 can include one ormore polymeric membrane materials having capabilities of limitinganalyte flux to active area 218 (i.e., membrane 220 is a mass transportlimiting membrane having some permeability for the analyte of interest).According to the disclosure herein, membrane 220 can be crosslinked witha branched crosslinker in certain particular sensor configurations. Thecomposition and thickness of membrane 220 can vary to promote a desiredanalyte flux to active area 218, thereby providing a desired signalintensity and stability. Analyte sensor 200 can be operable for assayingan analyte by any of coulometric, amperometric, voltammetric, orpotentiometric electrochemical detection techniques.

FIGS. 18B and 18C show diagrams of illustrative three-electrode analytesensor configurations, which are also compatible for use in thedisclosure herein. Three-electrode analyte sensor configurations can besimilar to that shown for analyte sensor 200 in FIG. 18A, except for theinclusion of additional electrode 217 in analyte sensors 201 and 202(FIGS. 18B and 18C). With additional electrode 217, counter/referenceelectrode 30216 can then function as either a counter electrode or areference electrode, and additional electrode 217 fulfills the otherelectrode function not otherwise accounted for. Working electrode 214continues to fulfill its original function. Additional electrode 217 canbe disposed upon either working electrode 214 or electrode 30216, with aseparating layer of dielectric material in between. For example, and notby the way of limitation, as depicted in FIG. 18B, dielectric layers 219a, 219 b and 219 c separate electrodes 214, 30216 and 217 from oneanother and provide electrical isolation. Alternatively, at least one ofelectrodes 214, 30216 and 217 can be located upon opposite faces ofsubstrate 30212, as shown in FIG. 18C. Thus, in certain embodiments,electrode 214 (working electrode) and electrode 30216 (counterelectrode) can be located upon opposite faces of substrate 30212, withelectrode 217 (reference electrode) being located upon one of electrodes214 or 30216 and spaced apart therefrom with a dielectric material.Reference material layer 30230 (e.g., Ag/AgCl) can be present uponelectrode 217, with the location of reference material layer 30230 notbeing limited to that depicted in FIGS. 18B and 18C. As with sensor 200shown in FIG. 18A, active area 218 in analyte sensors 201 and 202 caninclude multiple spots or a single spot. Additionally, analyte sensors201 and 202 can be operable for assaying an analyte by any ofcoulometric, amperometric, voltammetric, or potentiometricelectrochemical detection techniques.

Like analyte sensor 200, membrane 220 can also overcoat active area 218,as well as other sensor components, in analyte sensors 201 and 202,thereby serving as a mass transport limiting membrane. In certainembodiments, the additional electrode 217 can be overcoated withmembrane 220. Although FIGS. 18B and 18C have depicted electrodes 214,30216 and 217 as being overcoated with membrane 220, it is to berecognized that in certain embodiments only working electrode 214 isovercoated. Moreover, the thickness of membrane 220 at each ofelectrodes 214, 30216 and 217 can be the same or different. As intwo-electrode analyte sensor configurations (FIG. 18A), one or bothfaces of analyte sensors 201 and 202 can be overcoated with membrane 220in the sensor configurations of FIGS. 18B and 18C, or the entirety ofanalyte sensors 201 and 202 can be overcoated. Accordingly, thethree-electrode sensor configurations shown in FIGS. 18B and 18C shouldbe understood as being non-limiting of the embodiments disclosed herein,with alternative electrode and/or layer configurations remaining withinthe scope of the present disclosure.

FIG. 19A shows an illustrative configuration for sensor 203 having asingle working electrode with two different active areas disposedthereon. FIG. 19A is similar to FIG. 19A, except for the presence of twoactive areas upon working electrode 214: first active area 218 a andsecond active area 218 b, which are responsive to different analytes andare laterally spaced apart from one another upon the surface of workingelectrode 214. Active areas 218 a and 218 b can include multiple spotsor a single spot configured for detection of each analyte. Thecomposition of membrane 220 can vary or be compositionally the same atactive areas 218 a and 218 b. First active area 218 a and second activearea 218 b can be configured to detect their corresponding analytes atworking electrode potentials that differ from one another, as discussedfurther below. In certain embodiments, any one of active areas 218 a and218 b, or both, can be configured to detect an analyte using anNAD(P)-dependent enzyme. In certain embodiments, any one of active areas218 a and 218 b, or both, can be configured to detect an analyte usingan NAD(P)-dependent enzyme, e.g., ketones by using an enzyme systemcomprising NADH oxidase and β-hydroxybutyrate dehydrogenase. In certainembodiments, only one active area of 218 a and 218 b is configured todetect an analyte using an NAD(P)-dependent enzyme. In certainembodiments, the other active area is configured to detect a secondanalyte not using an NAD(P)-dependent enzyme.

FIGS. 19B and 19C show cross-sectional diagrams of illustrativethree-electrode sensor configurations for sensors 204 and 205,respectively, each featuring a single working electrode having firstactive area 218 a and second active area 218 b disposed thereon. FIGS.19B and 19C are otherwise similar to FIGS. 18B and 18C and can be betterunderstood by reference thereto. As with FIG. 19A, the composition ofmembrane 220 can vary or be compositionally the same at active areas 218a and 218 b.

Illustrative sensor configurations having multiple working electrodes,specifically two working electrodes, are described in further detail inreference to FIGS. 20-21C. Although the following description isprimarily directed to sensor configurations having two workingelectrodes, it is to be appreciated that more than two workingelectrodes can be incorporated through extension of the disclosureherein. Additional working electrodes can be used to impart additionalsensing capabilities to the analyte sensors beyond just a first analyteand a second analyte, e.g., for the detection of a third and/or fourthanalyte.

FIG. 20 shows a cross-sectional diagram of an illustrative analytesensor configuration having two working electrodes, a referenceelectrode and a counter electrode, which is compatible for use in thedisclosure herein. As shown, analyte sensor 300 includes workingelectrodes 304 and 306 disposed upon opposite faces of substrate 302.First active area 310 a is disposed upon the surface of workingelectrode 304, and second active area 310 b is disposed upon the surfaceof working electrode 306. Counter electrode 320 is electrically isolatedfrom working electrode 304 by dielectric layer 322, and referenceelectrode 321 is electrically isolated from working electrode 306 bydielectric layer 323. Outer dielectric layers 330 and 332 are positionedupon reference electrode 321 and counter electrode 320, respectively.Membrane 340 can overcoat at least active areas 310 a and 310 b,according to various embodiments, with other components of analytesensor 300 or the entirety of analyte sensor 300 optionally beingovercoated with first membrane portion 340 a and/or second membraneportion 340 b as well. Again, membrane 340 can be continuous but varycompositionally within first membrane portion 340 a and second membraneportion 340 b (i.e., upon active areas 310 a and 310 b) in order toafford different permeability values for differentially regulating theanalyte flux at each location. For example, different membraneformulations can be sprayed and/or printed onto the opposing faces ofanalyte sensor 300. Dip coating techniques can also be appropriate,particularly for depositing at least a portion of a bilayer membraneupon one of active areas 310 a and 310 b. Accordingly, one of firstmembrane portion 340 a and second membrane portion 340 b can comprise abilayer membrane and the other of first membrane portion 340 a andsecond membrane portion 340 b can comprise a single membrane polymer,according to particular embodiments of the present disclosure. Likeanalyte sensors 200, 201 and 202, analyte sensor 300 can be operable forassaying ketones (and/or a second analyte) by any of coulometric,amperometric, voltammetric, or potentiometric electrochemical detectiontechniques. In certain embodiments, an analyte sensor can include morethan one membrane 340, e.g., two or more membranes. For example, but notby way of limitation, an analyte sensor can include a membrane thatovercoats the one or more active areas, e.g., 310 a and 310 a, and anadditional membrane that overcoats the entire sensor as shown in FIG.20. In certain embodiments, any one of active areas 310 a and 310 b, orboth, can be configured to detect an analyte using an NAD(P)-dependentenzyme, e.g., ketones by using an enzyme system comprising NADH oxidaseand β-hydroxybutyrate dehydrogenase or β-hydroxybutyrate dehydrogenaseand diaphorase. In certain embodiments, only one active area of 310 aand 310 b is configured to detect an analyte using an NAD(P)-dependentenzyme, e.g., ketones by using an enzyme system comprising NADH oxidaseand β-hydroxybutyrate dehydrogenase or β-hydroxybutyrate dehydrogenaseand diaphorase. In certain embodiments, the other active area isconfigured to detect a second analyte, e.g., that is not detected usingan NAD(P)-dependent enzyme.

Alternative sensor configurations having multiple working electrodes anddiffering from the configuration shown in FIG. 20 can feature acounter/reference electrode instead of separate counter and referenceelectrodes 320, 321, and/or feature layer and/or membrane arrangementsvarying from those expressly depicted. For example, and not by the wayof limitation the positioning of counter electrode 320 and referenceelectrode 321 can be reversed from that depicted in FIG. 20. Inaddition, working electrodes 304 and 306 need not necessarily resideupon opposing faces of substrate 302 in the manner shown in FIG. 20.

Although suitable sensor configurations can feature electrodes that aresubstantially planar in character, it is to be appreciated that sensorconfigurations featuring non-planar electrodes can be advantageous andparticularly suitable for use in the disclosure herein. In particular,substantially cylindrical electrodes that are disposed concentricallywith respect to one another can facilitate deposition of a masstransport limiting membrane, as described hereinbelow. In particular,concentric working electrodes that are spaced apart along the length ofa sensor tail can facilitate membrane deposition through sequential dipcoating operations, in a similar manner to that described above forsubstantially planar sensor configurations. FIGS. 21A-21C showperspective views of analyte sensors featuring two working electrodesthat are disposed concentrically with respect to one another. It is tobe appreciated that sensor configurations having a concentric electrodedisposition but lacking a second working electrode are also possible inthe present disclosure.

FIG. 21A shows a perspective view of an illustrative sensorconfiguration in which multiple electrodes are substantially cylindricaland are disposed concentrically with respect to one another about acentral substrate. As shown, analyte sensor 400 includes centralsubstrate 402 about which all electrodes and dielectric layers aredisposed concentrically with respect to one another. In particular,working electrode 410 is disposed upon the surface of central substrate402, and dielectric layer 412 is disposed upon a portion of workingelectrode 410 distal to sensor tip 404. Working electrode 420 isdisposed upon dielectric layer 412, and dielectric layer 422 is disposedupon a portion of working electrode 420 distal to sensor tip 404.Counter electrode 430 is disposed upon dielectric layer 422, anddielectric layer 432 is disposed upon a portion of counter electrode 430distal to sensor tip 404. Reference electrode 440 is disposed upondielectric layer 432, and dielectric layer 442 is disposed upon aportion of reference electrode 440 distal to sensor tip 404. As such,exposed surfaces of working electrode 410, working electrode 420,counter electrode 430, and reference electrode 440 are spaced apart fromone another along longitudinal axis B of analyte sensor 400.

Referring still to FIG. 21A, first active areas 414 a and second activeareas 414 b, which are responsive to different analytes or the sameanalyte, are disposed upon the exposed surfaces of working electrodes410 and 420, respectively, thereby allowing contact with a fluid to takeplace for sensing. In certain embodiments, any one of active areas 414 aand 414 b, or both, can be configured to detect an analyte using anNAD(P)-dependent enzyme. In certain embodiments, any one of active areas414 a and 414 b, or both, can be configured to detect ketones, e.g., byusing an enzyme system comprising NADH oxidase and β-hydroxybutyratedehydrogenase. In certain embodiments, only one active area of 414 a and414 b is configured to detect ketones, e.g., by using an enzyme systemcomprising NADH oxidase and β-hydroxybutyrate dehydrogenase. In certainembodiments, the other active area is configured to detect a secondanalyte. In certain embodiments, any one of active areas 414 a and 414b, or both, can be configured to detect an analyte using anNAD(P)-dependent enzyme, e.g., ketones by using an enzyme systemcomprising NADH oxidase and β-hydroxybutyrate dehydrogenase orβ-hydroxybutyrate dehydrogenase and diaphorase. In certain embodiments,only one active area of 414 a and 414 b is configured to detect ananalyte using an NAD(P)-dependent enzyme, e.g., ketones by using anenzyme system comprising NADH oxidase and β-hydroxybutyratedehydrogenase or β-hydroxybutyrate dehydrogenase and diaphorase. Incertain embodiments, the other active area is configured to detect asecond analyte, e.g., that is not detected using an NAD(P)-dependentenzyme. Although active areas 414 a and 414 b have been depicted asthree discrete spots in FIG. 21A, it is to be appreciated that fewer orgreater than three spots, including a continuous layer of active area,can be present in alternative sensor configurations.

In FIG. 21A, sensor 400 is partially coated with membrane 450 uponworking electrodes 410 and 420 and active areas 414 a and 414 b disposedthereon. FIG. 21B shows an alternative sensor configuration in which thesubstantial entirety of sensor 401 is overcoated with membrane 450.Membrane 450 can be the same or vary compositionally at active areas 414a and 414 b. For example, membrane 450 can include a bilayer overcoatingactive areas 414 a and be a homogeneous membrane overcoating activeareas 414 b. In certain embodiments, one or more membranes are depositedover the exposed electroactive surface, e.g., platinum surface, of aworking electrode, including an interference domain and a mass transportlimiting membrane. For example, but not by way of limitation, aninterference domain can be disposed upon the working electrode, anactive area can be disposed upon the interference domain and a masstransport limiting membrane can be disposed upon the active area.

It is to be further appreciated that the positioning of the variouselectrodes in FIGS. 21A and 21B can differ from that expressly depicted.For example, the positions of counter electrode 430 and referenceelectrode 440 can be reversed from the depicted configurations in FIGS.21A and 21B. Similarly, the positions of working electrodes 410 and 420are not limited to those that are expressly depicted in FIGS. 21A and21B. FIG. 21C shows an alternative sensor configuration to that shown inFIG. 21B, in which sensor 405 contains counter electrode 430 andreference electrode 440 that are located more proximal to sensor tip 404and working electrodes 410 and 420 that are located more distal tosensor tip 404. Sensor configurations in which working electrodes 410and 420 are located more distal to sensor tip 404 can be advantageous byproviding a larger surface area for deposition of active areas 414 a and414 b (five discrete sensing spots illustratively shown in FIG. 21C),thereby facilitating an increased signal strength in some cases.Similarly, central substrate 402 can be omitted in any concentric sensorconfiguration disclosed herein, wherein the innermost electrode caninstead support subsequently deposited layers.

In certain embodiments, one or more electrodes of an analyte sensordescribed herein is a wire electrode, e.g., a permeable wire electrode.In certain embodiments, the sensor tail comprises a working electrodeand a reference electrode helically wound around the working electrode.In certain embodiments, an insulator is disposed between the working andreference electrodes. In certain embodiments, portions of the electrodesare exposed to allow reaction of the one or more enzymes with an analyteon the electrode. In certain embodiments, each electrode is formed froma fine wire with a diameter of from about 0.001 inches or less to about0.010 inches or more. In certain embodiments, the working electrode hasa diameter of from about 0.001 inches or less to about 0.010 inches ormore, e.g., from about 0.002 inches to about 0.008 inches, and morepreferably from about 0.004 inches to about 0.005 inches. In certainembodiments, an electrode is formed from a plated insulator, a platedwire or bulk electrically conductive material. In certain embodiments,the working electrode comprises a wire formed from a conductivematerial, such as platinum, platinum-iridium, palladium, graphite, gold,carbon, conductive polymer, alloys or the like. In certain embodiments,the conductive material is a permeable conductive material. In certainembodiments, the electrodes can by formed by a variety of manufacturingtechniques (e.g., bulk metal processing, deposition of metal onto asubstrate or the like), the electrodes can be formed from plated wire(e.g., platinum on steel wire) or bulk metal (e.g., platinum wire). Incertain embodiments, the electrode is formed from tantalum wire coveredwith platinum.

In certain embodiments, the reference electrode, which can function as areference electrode alone, or as a dual reference and counter electrode,is formed from silver, silver/silver chloride or the like. In certainembodiments, the reference electrode is juxtaposed and/or twisted withor around the working electrode. In certain embodiments, the referenceelectrode is helically wound around the working electrode. In certainembodiments, the assembly of wires can be coated or adhered togetherwith an insulating material so as to provide an insulating attachment.

In certain embodiments, additional electrodes can be included in thesensor tail. For example, but not by way of limitation, athree-electrode system (a working electrode, a reference electrode and acounter electrode) and/or an additional working electrode (e.g., anelectrode for detecting a second analyte). In certain embodiments wherethe sensor comprises two working electrodes, the two working electrodescan be juxtaposed around which the reference electrode is disposed upon(e.g., helically wound around the two or more working electrodes). Incertain embodiments, the two or more working electrodes can extendparallel to each other. In certain embodiments, the reference electrodeis coiled around the working electrode and extends towards the distalend (i.e., in vivo end) of the sensor tail. In certain embodiments, thereference electrode extends (e.g., helically) to the exposed region ofthe working electrode.

In certain embodiments, one or more working electrodes are helicallywound around a reference electrode. In certain embodiments where two ormore working electrodes are provided, the working electrodes can beformed in a double-, triple-, quad-, etc. helix configuration along thelength of the sensor tail (for example, surrounding a referenceelectrode, insulated rod or other support structure). In certainembodiments, the electrodes, e.g., two or more working electrodes, arecoaxially formed. For example, but not by way limitation, the electrodesall share the same central axis.

In certain embodiments, the working electrode comprises a tube with areference electrode disposed or coiled inside, including an insulatortherebetween. Alternatively, the reference electrode comprises a tubewith a working electrode disposed or coiled inside, including aninsulator therebetween. In certain embodiments, a polymer (e.g.,insulating) rod is provided, wherein the one or more electrodes (e.g.,one or more electrode layers) are disposed upon (e.g., byelectro-plating). In certain embodiments, a metallic (e.g., steel ortantalum) rod or wire is provided, coated with an insulating material(described herein), onto which the one or more working and referenceelectrodes are disposed upon. For example, but not by way of limitation,the present disclosure provides a sensor, e.g., a sensor tail, thatcomprises one or more tantalum wires, where platinum is disposed upon aportion of the one or more tantalum wires to function as a workingelectrode. In certain embodiments, the platinum-clad tantalum wire iscovered with an insulating material, where the insulating material ispartially covered with a silver/silver chloride composition to functionas a reference and/or counter electrode.

In certain embodiments where an insulator is disposed upon the workingelectrode (e.g., upon the platinum surface of the electrode), a portionof the insulator can be stripped or otherwise removed to expose theelectroactive surface of the working electrode. For example, but not byway of limitation, a portion of the insulator can be removed by hand,excimer lasing, chemical etching, laser ablation, grit-blasting or thelike. Alternatively, a portion of the electrode can be masked prior todepositing the insulator to maintain an exposed electroactive surfacearea. In certain embodiments, the portion of the insulator that isstripped and/or removed can be from about 0.1 mm (about 0.004 inches) orless to about 2 mm (about 0.078 inches) or more in length, e.g., fromabout 0.5 mm (about 0.02 inches) to about 0.75 mm (0.03 inches) inlength. In certain embodiments, the insulator is a non-conductivepolymer. In certain embodiments, the insulator comprises parylene,fluorinated polymers, polyethylene terephthalate, polyvinylpyrrolidone,polyurethane, polyimide and other non-conducting polymers. In certainembodiments, glass or ceramic materials can also be used in theinsulator layer. In certain embodiments, the insulator comprisesparylene. In certain embodiments, the insulator comprises apolyurethane. In certain embodiments, the insulator comprises apolyurethane and polyvinylpyrrolidone.

Several parts of the sensor are further described below.

2. NAD(P) Depot

The present disclosure provides analyte sensors that can include aninternal supply of a cofactor. For example, but not by way oflimitation, the present disclosure provides analyte sensors that caninclude an internal supply of a cofactor that allows the controlledrelease of the cofactor over an extended period of the time.

In certain embodiments, the cofactor internal supply can be coated withor distributed within a permeable layer that controls diffusion of thecofactor from the cofactor supply to maintain a sufficient concentrationof the cofactor in an active area, e.g., sensing chemistry layer, duringuse of the analyte sensor. The exact nature, size and configuration ofthe cofactor depot present within an analyte sensor can vary based onthe particular application of the analyte sensor, e.g., which analyte isbeing detected, the duration of analyte detection and the conditionsunder which the detection of the analyte occurs.

In certain embodiments, the cofactor is NAD or NADP (both of which arereferred to herein collectively as “NAD(P)”). In certain embodiments,the NAD(P) is a derivative of NAD(P). Non-limiting examples of NAD(P)derivatives are disclosed in WO 2007/012494 and WO 1998/033936, thecontents of each which are disclosed herein in their entireties. Incertain embodiments, the present disclosure provides analyte sensorsthat can include an internal supply of NAD(P) that allows the controlledrelease of NAD(P) or derivative thereof over an extended period of thetime. In certain embodiments, the NAD(P) internal supply can be coatedwith or distributed within a permeable layer that controls diffusion ofNAD(P) from the NAD(P) supply to maintain a sufficient concentration ofNAD(P) in an active area, e.g., sensing chemistry layer, comprising oneor more NAD(P)-dependent enzymes during use of the analyte sensor.

Non-limiting embodiments of analyte sensors that include an NAD(P) depotare provided in FIGS. 22 and 23A. For example, but not by way oflimitation, NAD(P) can be deposited onto a substrate, e.g., a plasticsubstrate, as shown in FIGS. 22 and 23A. In certain embodiments, anNAD(P) depot can be disposed on substrate 30212. In certain embodiments,an NAD(P) depot can be deposited between dielectric material, e.g., twodielectric layers, as shown in FIG. 23A.

In certain embodiments, the deposited NAD(P) can be overlaid with apermeable layer. As shown in FIGS. 22 and 23A, the NAD(P) depot is atleast partially coated with a permeable layer. For example, but not byway of limitation, at least about 10%, at least about 20%, at leastabout 30%, at least about 40%, at least about 50%, at least about 60%,at least about 70%, at least about 80%, at least about 90% or at leastabout 95% of the NAD(P) depot is coated with a permeable layer. Incertain embodiments, the NAD(P) depot is entirely coated with apermeable layer. In certain embodiments, the permeable layer providessustained NAD(P) release over time. The composition of the permeablelayer can vary depending on the desired release kinetics of the NAD(P),e.g., rate of NAD(P) release, from the internal supply.

Alternatively or additionally, NAD(P) can be present within thepermeable layer. For example, but not by way of limitation, NAD(P) canbe mixed directly into the permeable layer, e.g., polymer permeablelayer, rather than added as a separate layer coated by the permeablelayer. In certain embodiments, an analyte sensor of the presentdisclosure can include a permeable layer comprising NAD(P) disposed onsubstrate 30212. In certain embodiments, an analyte sensor of thepresent disclosure can include an NAD(P) depot disposed on substrate30212 that is overlaid with a permeable layer that includes a separatesupply of NAD(P).

In certain embodiments, the analyte sensor further includes a workingelectrode, e.g., 214, 30216 and/or 217, that is permeable. In certainembodiments, the permeable working electrode is disposed over thepermeable layer as shown in FIGS. 22 and 23A. In certain embodiments, atleast one active area (which contains the sensing chemistry) is disposedupon the working electrode as described herein. In certain embodiments,two or more active areas are disposed upon the working electrode asdescribed herein. In the non-limiting exemplary embodiments shown inFIGS. 22 and 23A, NAD(P) diffuses through the permeable layer, e.g.,polymer layer, and the permeable working electrode to contact the activearea to maintain a sufficient NAD(P) concentration in the active areaover time.

In certain embodiments, the amount of NAD(P) present within a NAD(P)depot can vary depending on the duration of use of the analyte sensor.For example, but not by way of limitation, NAD(P) can be present in anNAD(P) depot from about 0.1 μg to about 1,000 μg. In certainembodiments, from about 0.1 μg to about 900 μg, from about 0.1 μg toabout 800 μg, from about 0.1 μg to about 700 μg, from about 0.1 μg toabout 600 μg, from about 0.1 μg to about 500 μg, from about 0.1 μg toabout 400 μg, from about 0.1 μg to about 300 μg, from about 0.1 μg toabout 200 μg, from about 0.1 μg to about 100 μg, from about 0.1 μg toabout 90 μg, from about 0.1 μg to about 80 μg, from about 0.1 μg toabout 70 μg, from about 0.1 μg to about 60 μg, from about 0.1 μg toabout 50 μg, from about 0.1 μg to about 40 μg, from about 0.1 μg toabout 30 μg, from about 0.1 μg to about 20 μg, from about 0.1 μg toabout 10 μg, from about 0.1 μg to about 9 μg, from about 0.1 μg to about8 μg, from about 0.1 μg to about 7 μg, from about 0.1 μg to about 6 μg,from about 0.1 μg to about 5 μg, from about 0.1 μg to about 4 μg, fromabout 0.1 μg to about 3 μg, from about 0.1 μg to about 2 μg, from about0.1 μg to about 1 μg, from about 0.1 μg to about 0.9 μg, from about 0.1μg to about 0.8 μg, from about 0.1 μg to about 0.7 μg, from about 0.1 μgto about 0.6 μg, from about 0.1 μg to about 0.5 μg, from about 0.1 μg toabout 0.4 μg, from about 0.1 μg to about 0.3 μg, from about 0.1 μg toabout 0.2 μg, from about 0.2 μg to about 1,000 μg, from about 0.3 μg toabout 1,000 μg, from about 0.4 μg to about 1,000 μg, from about 0.5 μgto about 1,000 μg, from about 0.6 μg to about 1,000 μg, from about 0.7μg to about 1,000 μg, from about 0.8 μg to about 1,000 μg, from about0.9 μg to about 1,000 μg, from about 1 μg to about 1,000 μg, from about2 μg to about 1,000 μg, from about 3 μg to about 1,000 μg, from about 4μg to about 1,000 μg, from about 5 μg to about 1,000 μg, from about 6 μgto about 1,000 μg, from about 7 μg to about 1,000 μg, from about 8 μg toabout 1,000 μg, from about 9 μg to about 1,000 μg, from about 10 μg toabout 1,000 μg, from about 11 μg to about 1,000 μg, from about 12 μg toabout 1,000 μg, from about 13 μg to about 1,000 μg, from about 14 μg toabout 1,000 μg, from about 15 μg to about 1,000 μg, from about 16 μg toabout 1,000 μg, from about 17 μg to about 1,000 μg, from about 18 μg toabout 1,000 μg, from about 19 μg to about 1,000 μg, from about 20 μg toabout 1,000 μg, from about 30 μg to about 1,000 μg, from about 40 μg toabout 1,000 μg, from about 50 μg to about 1,000 μg, from about 60 μg toabout 1,000 μg, from about 70 μg to about 1,000 μg, from about 80 μg toabout 1,000 μg, from about 90 μg to about 1,000 μg, from about 100 μg toabout 1,000 μg, from about 200 μg to about 1,000 μg, from about 300 μgto about 1,000 μg, from about 400 μg to about 1,000 μg, from about 500μg to about 1,000 μg, from about 600 μg to about 1,000 μg, from about700 μg to about 1,000 μg, from about 800 μg to about 1,000 μg, fromabout 900 μg to about 1,000 μg, from about 0.1 μg to about 100 μg, fromabout 1 μg to about 100 μg, from about 1 μg to about 90 μg, from about 1μg to about 80 μg, from about 1 μg to about 70 μg, from about 1 μg toabout 60 μg, from about 1 μg to about 50 μg, from about 1 μg to about 40μg, from about 1 μg to about 30 μg, from about 1 μg to about 20 μg, fromabout 1 μg to about 15 μg, from about 1 μg to about 10 μg or from about5 μg to about 15 μg NAD(P) can be present in an NAD(P) depot. In certainembodiments, NAD(P) can be present in an NAD(P) depot from about 0.1 μgto about 100 μg.

In certain embodiments, the amount of NAD(P) present in the NAD(P) depotvaries depending on the lifetime of the analyte sensor. For example, butnot by way of limitation, the amount of NAD(P) in the NAD(P) depotallows the analyte sensor to detect an analyte using an NAD(P)-dependentenzyme for at least about 7 days, for at least about 8 days, for atleast about 9 days, for at least about 10 days, for at least about 11days, for at least about 12 days, for at least about 13 days, for atleast about 14 days, for at least about 15 days, for at least about 16days, for at least about 17 days, for at least about 18 days, for atleast about 19 days, for at least about 20 days, for at least about 25days, for at least about 30 days, for at least about 35 days or for atleast about 40 days. In certain embodiments, the amount of NAD(P) in theNAD(P) depot allows the analyte sensor to detect an analyte using anNAD(P)-dependent enzyme for at least about 14 days. In certainembodiments, the amount of NAD(P) in the NAD(P) depot allows the analytesensor to detect an analyte using an NAD(P)-dependent enzyme for greaterthan about two weeks, for greater than about three weeks, for greaterthan about four weeks, for greater than about five weeks, for greaterthan about six weeks, for greater than about seven weeks or for greaterthan about eight weeks.

In certain embodiments, the permeable layer can include a polymer. Incertain embodiments, the permeable polymer layer can include adiffusion-controlling polymer. In certain embodiments, the permeablepolymer layer can include any polymer that allows controlled diffusionof a cofactor. In certain embodiments, the permeable polymer layer caninclude any polymer that allows controlled diffusion of NAD(P) thereof.

In certain embodiments, the permeable polymer layer can includehyaluronic acid (HA), poly(ethylene glycol) (PEG), phosphoryl cholinebased polymers and other hydrophilic polymers having a hydrophilicitycomparable to HA, PEG, or phosphoryl choline, ethylene vinyl alcoholcopolymer, polyhydroxyalkanoate, poly(hydroxyvalerate),polycaprolactone, poly(lactide-co-glycolide), poly(hydroxybutyrate),poly(hydroxybutyrate-co-valerate), polydioxanone, polyorthoester,polyanhydride, poly(glycolic acid), poly(D,L-lactic acid) (DLPLA),poly(ortho esters), poly(glycolic acid-co-trimethylene carbonate),polyphosphoester, polyphosphoester urethane, poly(amino acids),cyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate),polyurethanes, copoly(ether-esters) (e.g., PEO/PLA), polyalkyleneoxalates, polyphosphazenes, biomolecules, such as fibrin, fibrinogen,cellulose, starch and collagen, polyurethanes, silicones, polyesters,polyolefins, polyisobutylene and ethylene-alphaolefin copolymers,acrylic polymers and copolymers, vinyl halide polymers and copolymers,poly(amide ester) (PEA), polycaprolactone (PCL), poly(hexafluoropropylene) (HFP), poly(ethylene vinyl alcohol) (EVAL), polyvinyl etherssuch as polyvinyl methyl ether, polyvinylidene halides such aspolyvinylidene fluoride (PVDF) and polyvinylidene chloride,polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics such aspolystyrene, polyvinyl esters such as polyvinyl acetate, copolymers ofvinyl monomers with each other and olefins such as ethylene-methylmethacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins,and ethylene-vinyl acetate copolymers, polyamides such as Nylon 66 andpolycaprolactam, alkyd resins, polycarbonates, polyoxymethylenes,polyimides, polyethers, epoxy resins, polyurethanes, rayon,rayon-triacetate, cellulose acetate, cellulose butyrate, celluloseacetate butyrate, cellophane, cellulose nitrate, cellulose propionate,cellulose ethers and carboxymethyl cellulose. In certain embodiments, asuitable polymer is a copolymer comprising a poly(ethylene glycolterephthalate) and poly(butylene terephthalate) (PEGT/PBT) segments.

Further non-limiting examples of polymers that can be present in thepermeable layer include polycarboxylic acids, cellulosic polymers,gelatin, polyvinylpyrrolidone, cross-linked polyvinylpyrrolidone,polyanhydrides including maleic anhydride polymers, polyvinyl alcohols,polyvinyl aromatics such as copolymers of polystyrene with other vinylmonomers such as isobutylene, isoprene and butadiene, for example,styrene-isobutylene-styrene (SIBS), styrene-isoprene-styrene (SIS)copolymers, styrene-butadiene-styrene (SBS) copolymers, polyethyleneoxides, glycosaminoglycans, polysaccharides, polyesters includingpolyethylene terephthalate, polyacrylamides, polyether sulfone,polyalkylenes including polypropylene, polyethylene and high molecularweight polyethylene, halogenated polyalkylenes includingpolytetrafluoroethylene, natural and synthetic rubbers includingpolyisoprene, polybutadiene, polyisobutylene and copolymers thereof withother vinyl monomers such as polyorthoesters, proteins, polypeptides,siloxane polymers, polylactic acid, polyglycolic acid,polyhydroxybutyrate valerate and blends and copolymers thereof as wellas other biodegradable, bioabsorbable and biostable polymers andcopolymers. In certain embodiments, suitable polymers includepolyacrylic acid and a copolymer of polylactic acid andpolycaprolactone.

In certain embodiments, the permeable layer can include apolyether-based polymer. In certain embodiments, the permeable layer caninclude a poly(ethylene glycol). In certain embodiments, the permeablelayer can include a poly(ethylene glycol)-based polymer. In certainembodiments, the permeable layer can include a poly(propylene glycol).In certain embodiments, the permeable layer can include a poly(propyleneglycol)-based polymer. In certain embodiments, the permeable layer caninclude poly(propylene glycol) methacrylate (POMA). In certainembodiments, the permeable layer can include 2-hydroxyethyl methacrylate(HEMA). In certain embodiments, the permeable layer can include amixture of POMA and HEMA. In certain embodiments, the permeable layercan include a mixture of POMA and HEMA to generate the permeablepolymer. For example, but not by way of limitation, the permeable layercan include a ratio of POMA to HEMA from about 10:1 to about 1:10, e.g.,from about 9:1 to about 1:9, from about 8:1 to about 1:8, from about 7:1to about 1:7, from about 6:1 to about 1:6, from about 5:1 to about 1:5,from about 4:1 to about 1:4, from about 3:1 to about 1:3, from about 2:1to about 1:2. In certain embodiments, the ratio of POMA to HEMA can befrom about 2:1 to about 1:2. In certain embodiments, the ratio of POMAto HEMA can be about 1:1. In certain embodiments, the permeable layercan include from about 20% to about 80% by weight of POMA, e.g., fromabout 30% to about 70% or from about 40% to about 60% by weight. Incertain embodiments, the permeable layer can from about 40% to about 60%by weight of POMA. In certain embodiments, the permeable layer can fromabout 20% to about 80% by weight of HEMA, e.g., from about 30% to about70% or from about 40% to about 60% by weight. In certain embodiments,the permeable layer can from about 40% to about 60% by weight of HEMA.

In certain embodiments, the permeable polymer is a hydrogel. In certainembodiments, a permeable polymer, e.g., hydrogel, for use in the presentdisclosure is capable of absorbing from about 30% to about 95% of itsweight in water, e.g., from about 30% to about 70% or from about 40% toabout 60%. In certain embodiments, the permeable polymer, e.g.,hydrogel, is capable of absorbing at least about 30% of its weight inwater. In certain embodiments, the permeable polymer, e.g., hydrogel, iscapable of absorbing at least about 40% of its weight in water. Incertain embodiments, the permeable polymer, e.g., hydrogel, is capableof absorbing at least about 50% of its weight in water. In certainembodiments, the permeable polymer, e.g., hydrogel, is capable ofabsorbing at least about 60% of its weight in water. In certainembodiments, the permeable polymer, e.g., hydrogel, is capable ofabsorbing at least about 70% of its weight in water. In certainembodiments, the permeable polymer, e.g., hydrogel, is capable ofabsorbing from about 30% to about 60% of its weight in water.

In certain embodiments, the NAD(P) depot has a thickness, e.g., drythickness, ranging from about 0.1 μm to about 1,000 μm, e.g., from about1 μm to about 500 μm, about 10 μm to about 100 μm or about 10 μm toabout 100 μm. In certain embodiments, the NAD(P) depot can have athickness from about 0.1 μm to about 10 μm, e.g., from about 0.5 μm toabout 10 μm, from about 1 μm to about 10 μm, from about 1 μm to about 5μm or from about 0.1 μm to about 5 μm.

In certain embodiments, the permeable electrode can include any materialthat is permeable to NAD(P). In certain embodiments, the permeableelectrode can include any conductive material, e.g., conductive ink orpolymer, that is permeable to NAD(P). For example, but not by way oflimitation, the permeable electrode can include carbon, silver,amorphous carbon, graphite, graphene, glassy carbon, platinized carbon,gold, platinum and/or palladium. In certain embodiments, the permeableelectrode can include a carbon material. In certain embodiments, thepermeable electrode can include a carbon material that includes anadditive such as, but not limited to, silver, amorphous carbon,graphite, graphene, glassy carbon, platinized carbon, gold, platinumand/or palladium. In certain embodiments, the permeable electrode can beat least partially composed of a carbon nanotube. In certainembodiments, the permeable electrode can include a conductive polymer,e.g., poly(3,4-ethylenedioxythiophene) polystyrene sulfonate(PEDOT:PSS). In certain embodiments, the conductive material can bepresent in a polymer, e.g., a polymeric carrier. In certain embodiments,the electrode comprises a polymer comprising a conductive materialand/or conductive particles.

3. Enzymes

The sensors of the present disclosure include one or more enzymes fordetecting one or more analytes in at least one active area. Suitableenzymes for use in a sensor of the present disclosure include, but arenot limited to, any NAD(P)-dependent enzyme. For example, anNAD(P)-dependent enzyme for use in the present disclosure can be usedfor detecting glucose, ketones, lactate, oxygen, hemoglobin A1C,albumin, alcohol, alkaline phosphatase, alanine transaminase, aspartateaminotransferase, bilirubin, blood urea nitrogen, calcium, carbondioxide, chloride, creatinine, hematocrit, lactate, magnesium, oxygen,pH, phosphorus, potassium, sodium, total protein, uric acid, etc. Incertain embodiments, the analyte to be detected using anNAD(P)-dependent enzyme is glucose, lactate, ketones, creatinine,alcohol, e.g., ethanol, or the like. In certain embodiments, an activearea can include multiple enzymes, e.g., an enzyme system, that arecollectively responsive to the analyte.

In certain embodiments, an active area of a presently disclosed analytesensor includes at least one NAD(P)-dependent enzyme. In certainembodiments, an active area of a presently disclosed analyte sensorincludes two or more NAD(P)-dependent enzymes. In certain embodiments,an analyte sensor of the present disclosure includes two active sitesthat each include at least one NAD(P)-dependent enzyme. Alternatively,an analyte sensor of the present disclosure in certain embodimentsincludes two active sites, where only one active site includes anNAD(P)-dependent enzyme. Non-limiting examples of NAD(P)-dependentenzymes are disclosed in Vidal et al., Biochimica et BiophysicaActa—Proteins and Proteomics 1866(2):327-347 (2018) (see Tables 1-2),the contents of which are incorporated by reference herein.

In certain embodiments, an analyte sensor of the present disclosureincludes one or more internal supplies of NAD(P) for an NAD(P)-dependentenzyme included in one or more active sites of the analyte sensor. Forexample, but not by way of limitation, an NAD(P) depot can be disposedunderneath each electrode configured for detecting an analyte.Alternatively, an NAD(P) depot can be disposed underneath only oneelectrode that is configured for detecting an analyte.

In certain embodiments, an active site can include an NAD(P)-dependentdehydrogenase. Non-limiting examples of NAD(P)-dependent dehydrogenasesinclude glucose dehydrogenase (E.C.1.1.1.47), lactate dehydrogenase(EC1.1.1.27 and EC1.1.1.28), malate dehydrogenase (EC1.1.1.37), glyceroldehydrogenase (EC1.1.1.6), alcohol dehydrogenase (EC1.1.1.1),alpha-hydroxybutyrate dehydrogenase, sorbitol dehydrogenase, amino aciddehydrogenase such as L-amino acid dehydrogenase (EC1.4.1.5), diaphorase(EC1.8.1.4) and combinations thereof.

In certain embodiments, the NAD(P)-dependent dehydrogenase can includediaphorase, glucose dehydrogenase, alcohol dehydrogenase, lactatedehydrogenase and β-hydroxybutyrate dehydrogenase. In certainembodiments, the enzyme system can include two or more NAD(P)-dependentdehydrogenases, e.g., a first NAD(P)-dependent dehydrogenase anddiaphorase. For example, but not by way of limitation, theNAD(P)-dependent dehydrogenase can convert the analyte and oxidizednicotinamide adenine dinucleotide (NAD⁺) into an oxidized analyte andreduced nicotinamide adenine dinucleotide (NADH), respectively. Theenzyme cofactors NAD⁺ and NADH aid in promoting the concerted enzymaticreactions disclosed herein. The NADH can then undergo reduction underdiaphorase mediation, with the electrons transferred during this processproviding the basis for analyte detection at the working electrode.

In certain embodiments, an analyte sensor of the present disclosure caninclude a glucose-responsive active area, a ketones-responsive activearea, a lactate-responsive active area, a creatinine-responsive activearea, an alcohol-responsive active area or a combination thereof. Incertain embodiments, a glucose-responsive active area can include one ormore NAD(P)-dependent enzymes for detecting glucose. In certainembodiments, a ketones-responsive active area can include one or moreNAD(P)-dependent enzymes for detecting ketones. In certain embodiments,a lactate-responsive active area can include one or moreNAD(P)-dependent enzymes for detecting lactate. In certain embodiments,a creatinine-responsive active area can include one or moreNAD(P)-dependent enzymes for detecting creatinine. In certainembodiments, an alcohol-responsive active area can include one or moreNAD(P)-dependent enzymes for detecting alcohol. In certain embodiments,an active area can include an enzyme system comprising two or moreenzymes that are collectively responsive to the analyte. For example,but not by way of limitation, a ketones-responsive active area caninclude an enzyme system comprising at least one NAD(P)-dependentenzyme.

In certain embodiments, an active site can be a glucose-responsiveactive site that includes at least one NAD(P)-dependent enzyme fordetecting glucose. In certain embodiments, a glucose-responsive activesite can include a glucose dehydrogenase. For example, but not by way oflimitation, an analyte sensor of the present disclosure for detectingglucose can include an NAD(P) depot and an active area comprising aglucose dehydrogenase.

In certain embodiments, an active site can be an alcohol-responsiveactive site that includes at least one NAD(P)-dependent enzyme fordetecting one or more alcohols. In certain embodiments, analcohol-responsive active site can include an alcohol dehydrogenase. Forexample, but not by way of limitation, an analyte sensor of the presentdisclosure for detecting an alcohol can include an NAD(P) depot and anactive area comprising an alcohol dehydrogenase.

In certain embodiments, an active site can be a ketones-responsiveactive site that includes at least one NAD(P)-dependent enzyme fordetecting one or more ketones. In certain embodiments, aketones-responsive active site can include β-hydroxybutyratedehydrogenase. For example, but not by way of limitation, an analytesensor of the present disclosure for detecting ketones can include anNAD(P) depot and an active area comprising an enzyme system thatincludes β-hydroxybutyrate dehydrogenase.

In certain embodiments, an active site can be a lactate-responsiveactive site that includes at least one NAD(P)-dependent enzyme fordetecting lactate. For example, but not by way of limitation, alactate-responsive active site can include a lactate dehydrogenase. Incertain embodiments an analyte sensor of the present disclosure fordetecting lactate can include an NAD(P) depot and an active areacomprising a lactate dehydrogenase.

In certain embodiments, an analyte sensor disclosed herein can includeat least one active site that includes one or more NAD(P)-dependentenzymes, as disclosed herein, for detecting an analyte. Alternatively,an analyte sensor disclosed herein can include two or more active sites,with each active site contains one or more enzymes, e.g., where at leastone of the active sites includes one or more NAD(P)-dependent enzymes.For example, but not by way of limitation, an analyte sensor of thepresent disclosure can include a first active area that comprises afirst enzyme (or enzyme system) for use in detecting a first analyte anda second active site that includes a second enzyme (or second enzymesystem) for detecting a second analyte, where at least the first activearea or second active area includes an NAD(P)-dependent enzyme.

In certain embodiments, the analyte-responsive active area can includefrom about 10% to about 80% by weight, e.g., from about 15% to about75%, from about 20% to about 70%, from about 25% to about 65% or fromabout 30% to about 60% by weight, of one or more enzymes (e.g., one ormore NAD(P)-dependent enzymes) disclosed herein. In certain embodiments,the analyte-responsive active area can include from about 10% to about80% by weight, e.g., from about 15% to about 75%, from about 20% toabout 70%, from about 25% to about 65%, from about 30% to about 60% byweight, from about 20% to about 60% or from about 20% to about 50%, ofone or more enzymes (e.g., one or more NAD(P)-dependent enzymes)disclosed herein. In certain embodiments, the analyte-responsive activearea can include from about 10% to about 80% by weight, e.g., from about15% to about 75%, from about 20% to about 70%, from about 25% to about65% or from about 30% to about 60% by weight, of one or more enzymes(e.g., one or more NAD(P)-dependent enzymes) disclosed herein. Incertain embodiments, the analyte-responsive active area can include fromabout 10% to about 80% by weight, e.g., from about 15% to about 75%,from about 20% to about 70%, from about 25% to about 65% or from about30% to about 60% by weight, of one or more enzymes (e.g., one or moreNAD(P)-dependent enzymes) disclosed herein.

In certain embodiments, the analyte-responsive active area can furtherinclude a stabilizer, e.g., for stabilizing the enzyme. For example, butnot by way of limitation, the stabilizer can be an albumin, e.g., aserum albumin. Non-limiting examples of serum albumins include bovineserum albumin and human serum albumin. In certain embodiments, thestabilizer is a human serum albumin. In certain embodiments, thestabilizer is a bovine serum albumin. In certain embodiments, thestabilizer can be catalase. In certain embodiments, theanalyte-responsive active area can include a ratio of stabilizer to theone or more enzymes present in the analyte-responsive active area, e.g.,NAD(P)-dependent enzyme, from about 40:1 to about 1:40, e.g., from about35:1 to about 1:35, from about 30:1 to about 1:30, from about 25:1 toabout 1:25, from about 20:1 to about 1:20, from about 15:1 to about1:15, from about 10:1 to about 1:10, from about 9:1 to about 1:9, fromabout 8:1 to about 1:8, from about 7:1 to about 1:7, from about 6:1 toabout 1:6, from about 5:1 to about 1:5, from about 4:1 to about 1:4,from about 3:1 to about 1:3, from about 2:1 to about 1:2 or about 1:1.In certain embodiments, the analyte-responsive active area can include aratio of stabilizer to the one or more enzymes present in theanalyte-responsive active area, e.g., NAD(P)-dependent enzyme, fromabout 2:1 to about 1:2. In certain embodiments, the analyte-responsiveactive area can include a ratio of stabilizer to the NAD(P)-dependentenzyme, e.g., NAD(P)-dependent dehydrogenase, from about 40:1 to about1:40, e.g., from about 35:1 to about 1:35, from about 30:1 to about1:30, from about 25:1 to about 1:25, from about 20:1 to about 1:20, fromabout 15:1 to about 1:15, from about 10:1 to about 1:10, from about 9:1to about 1:9, from about 8:1 to about 1:8, from about 7:1 to about 1:7,from about 6:1 to about 1:6, from about 5:1 to about 1:5, from about 4:1to about 1:4, from about 3:1 to about 1:3, from about 2:1 to about 1:2or about 1:1. In certain embodiments, the analyte-responsive active areacan include a ratio of stabilizer to the NAD(P)-dependent enzyme, e.g.,NAD(P)-dependent dehydrogenase, from about 2:1 to about 1:2. In certainembodiments, the analyte-responsive active area can include from about10% to about 50%, e.g., from about 15% to about 45%, from about 20% toabout 40%, from about 20% to about 35% or from about 20% to about 30% byweight of the stabilizer. In certain embodiments, the analyte-responsiveactive area can include from about 15% to about 35% of the stabilizer byweight.

In certain embodiments, in addition to the presence of an NAD(P) depot,the analyte-responsive active area can further include a cofactor forone or more enzyme present in the analyte-responsive active area. Incertain embodiments, the cofactor is NAD(P). In certain embodiments, thecofactor is a cofactor different from NAD(P). In certain embodiments,the analyte-responsive active area can include a ratio of cofactor toenzyme from about 40:1 to about 1:40, e.g., from about 35:1 to about1:35, from about 30:1 to about 1:30, from about 25:1 to about 1:25, fromabout 20:1 to about 1:20, from about 15:1 to about 1:15, from about 10:1to about 1:10, from about 9:1 to about 1:9, from about 8:1 to about 1:8,from about 7:1 to about 1:7, from about 6:1 to about 1:6, from about 5:1to about 1:5, from about 4:1 to about 1:4, from about 3:1 to about 1:3,from about 2:1 to about 1:2 or about 1:1. In certain embodiments, theanalyte-responsive active area can include a ratio of cofactor to enzymefrom about 2:1 to about 1:2. In certain embodiments, theanalyte-responsive active area can include from about 10% to about 50%by weight, e.g., from about 15% to about 45%, from about 20% to about40%, from about 20% to about 35%, from about 20% to about 30% by weightof the cofactor. In certain embodiments, the analyte-responsive activearea can include from about 15% to about 35% by weight of the cofactor.In certain embodiments, the cofactor, e.g., NAD(P), can be physicallyretained within the analyte-responsive active area. For example, but notby way of limitation, a membrane overcoating the analyte-responsiveactive area can aid in retaining the cofactor within theanalyte-responsive active area while still permitting sufficient inwarddiffusion of the analyte to permit detection thereof.

In certain embodiments, an analyte sensor of the present disclosure caninclude a sensor tail comprising at least one NAD(P) depot, at least oneworking electrode, e.g., permeable electrode, and an analyte-responsiveactive area disposed upon the surface of the working electrode, wherethe analyte-responsive active area includes at least oneNAD(P)-dependent enzyme. In certain embodiments, an analyte sensor ofthe present disclosure can include a sensor tail comprising a substrate,at least one NAD(P) depot disposed upon a surface of the substrate, atleast one working electrode, e.g., permeable electrode, and ananalyte-responsive active area disposed upon the surface of the workingelectrode, where the analyte-responsive active area includes at leastone NAD(P)-dependent enzyme. In certain embodiments, theNAD(P)-dependent enzyme is an NAD(P)-dependent dehydrogenase. Forexample, but not by way of limitation, a sensor of the presentdisclosure can include a sensor tail comprising at least one NAD(P)depot, a permeable layer disposed upon the NAD(P) depot, at least onepermeable working electrode and an analyte-responsive active areadisposed upon the surface of the permeable working electrode, where theanalyte-responsive active area includes an enzyme system comprising anNAD(P) dependent-dehydrogenase.

In certain embodiments, a sensor of the present disclosure can include asensor tail comprising at least one NAD(P) depot, a permeable layerdisposed on top of the NAD(P) depot, at least one permeable workingelectrode and a ketones-responsive active area disposed upon the surfaceof the permeable working electrode, where the ketones-responsive activearea includes an enzyme system comprising an NAD(P)-dependentdehydrogenase, e.g., β-hydroxybutyrate dehydrogenase. In certainembodiments, the enzyme system further includes diaphorase.

In certain embodiments, an analyte sensor of the present disclosure caninclude a second active area, e.g., for detecting an analyte differentfrom the analyte detected by the first active area. In certainembodiments, the second active area is disposed upon the same workingelectrode as the first active area or on a second working electrode. Incertain embodiments, the second active area is a glucose-responsiveactive area, a lactate-responsive active area, a creatinine-responsiveactive area or an alcohol-responsive active area.

In certain embodiments, the second active area of an analyte sensor ofthe present disclosure can include one or more enzymes for detectingglucose. For example, but not by way of limitation, an analyte sensor ofthe present disclosure can include an active area (e.g., a second activearea) that comprises one or more enzymes for detecting glucose, e.g.,disposed on a second working electrode. In certain embodiments, theanalyte sensor can include an active site comprising a glucose oxidaseand/or a glucose dehydrogenase for detecting glucose.

In certain embodiments, the second active area can include one or moreenzymes for detecting lactate. For example, but not by way oflimitation, an analyte sensor of the present disclosure can include anactive area (e.g., a second active area) that comprises one or moreenzymes, e.g., an enzyme system, for detecting lactate, e.g., disposedon a second working electrode. In certain embodiments, the analytesensor can include an active site comprising a lactate dehydrogenaseand/or a lactate oxidase.

In certain embodiments, the second enzyme-responsive active area, e.g.,present on a second working electrode, of an analyte sensor of thepresent disclosure can include one or more enzymes for detectingalcohol. For example, but not by way of limitation, an analyte sensor ofthe present disclosure can include an active area (e.g., a second activearea) that comprises one or more enzymes, e.g., an enzyme system, fordetecting alcohol, e.g., disposed on a second working electrode. Incertain embodiments, the analyte sensor can include an active sitecomprising an alcohol dehydrogenase.

In certain embodiments, the second enzyme-responsive active area, e.g.,present on a second working electrode, of an analyte sensor of thepresent disclosure can include one or more enzymes for detectingcreatinine. For example, but not by way of limitation, an analyte sensorof the present disclosure can include an active area (e.g., a secondactive area) that comprises one or more enzymes, e.g., an enzyme system,for detecting creatinine, e.g., disposed on a second working electrode.In certain embodiments, the analyte sensor can include an active sitecomprising an amidohydrolase, creatine amidinohydrolase and/or sarcosineoxidase.

In certain embodiments, an analyte sensor can include two workingelectrodes, e.g., a first active area disposed on a first workingelectrode (e.g., permeable electrode) and a second active area disposedon a second working electrode. For example, but not by way oflimitation, an analyte sensor disclosed herein can feature at least oneNAD(P) depot, a first analyte-responsive active area disposed on a firstworking electrode and a second analyte-responsive active area disposedupon the surface of a different working electrode, e.g., second workingelectrode, where at least one of the analyte-responsive active areasincludes an NAD(P)-dependent enzyme. In certain embodiments, the secondanalyte-responsive active area can be configured to detect a differentanalyte or the same analyte detected by first analyte-responsive activearea. In certain embodiments, such analyte sensors can include a sensortail with at least one NAD(P) depot, a first working electrode and asecond working electrode, a first analyte-responsive active areadisposed upon a surface of the first working electrode and a secondanalyte-responsive active area disposed upon a surface of the secondworking electrode, where at least one of the analyte-responsive activeareas includes an NAD(P)-dependent enzyme and at least one of theworking electrodes is permeable. For example, but not by way oflimitation, the analyte-responsive active area that includes anNAD(P)-dependent enzyme is disposed upon the permeable workingelectrode.

In certain embodiments, when the sensor is configured to detect two ormore analytes using two working electrodes, detection of each analytecan include applying a potential to each working electrode separately,such that separate signals are obtained from each analyte. The signalobtained from each analyte can then be correlated to an analyteconcentration through use of a calibration curve or function, or byemploying a lookup table. In certain particular embodiments, correlationof the analyte signal to an analyte concentration can be conductedthrough use of a processor.

In certain other analyte sensor configurations, the first active areaand the second active area can be disposed upon a single workingelectrode. For example, but not by way of limitation, an analyte sensordisclosed herein can feature at least one NAD(P) depot, a firstanalyte-responsive active area and a second analyte-responsive activearea disposed upon the surface of a single permeable working electrode,where at least one of the analyte-responsive active areas includes anNAD(P)-dependent enzyme. In certain embodiments, a first signal can beobtained from the first active area, e.g., at a low potential, and asecond signal containing a signal contribution from both active areascan be obtained at a higher potential. Subtraction of the first signalfrom the second signal can then allow the signal contribution arisingfrom the second analyte to be determined. The signal contribution fromeach analyte can then be correlated to an analyte concentration in asimilar manner to that described for sensor configurations havingmultiple working electrodes. In certain embodiments, when aketones-responsive active area and the second active area configured todetect a different analyte, e.g., a glucose-responsive active area, arearranged upon a single working electrode in this manner, one of theactive areas can be configured such that it can be interrogatedseparately to facilitate detection of each analyte. For example, eitherthe ketones-responsive active area or glucose-responsive active area canproduce a signal independently of the other active area.

It is also to be appreciated that the sensitivity (output current) ofthe analyte sensors toward each analyte can be varied by changing thecoverage (area or size) of the active areas, the area ratio of theactive areas with respect to one another, the identity, thickness and/orcomposition of a mass transport limiting membrane overcoating the activeareas. Variation of these parameters can be conducted readily by onehaving ordinary skill in the art once granted the benefit of thedisclosure herein.

4. Redox Mediators

In certain embodiments, an analyte sensor disclosed herein can includean electron transfer agent. For example, but not by way of limitation,one or more active sites of an analyte sensor can include an electrontransfer agent. In certain embodiments, an analyte sensor can includeone active site that includes an electron transfer agent and a secondactive site that does not include an electron transfer agent. In certainembodiments, the presence of an electron transfer agent in an activearea can depend on the enzyme or enzyme system used to detect theanalyte and/or the composition of the working electrode. Alternatively,an analyte sensor can include two active sites, where both active sitesinclude an electron transfer agent.

Suitable electron transfer agents can facilitate conveyance of electronsto the adjacent working electrode after an analyte undergoes anenzymatic oxidation-reduction reaction within the corresponding activearea, thereby generating a current that is indicative of the presence ofthat particular analyte. The amount of current generated is proportionalto the quantity of analyte that is present. In certain embodiments,suitable electron transfer agents can include electroreducible andelectrooxidizable ions, complexes or molecules (e.g., quinones) havingoxidation-reduction potentials that are a few hundred millivolts aboveor below the oxidation-reduction potential of the standard calomelelectrode (SCE). In certain embodiments, the redox mediators can includeosmium complexes and other transition metal complexes, such as thosedescribed in U.S. Pat. Nos. 6,134,461 and 6,605,200, which areincorporated herein by reference in their entirety. Additional examplesof suitable redox mediators include those described in U.S. Pat. Nos.6,736,957, 7,501,053 and 7,754,093, the disclosures of each of which arealso incorporated herein by reference in their entirety. Other examplesof suitable redox mediators include metal compounds or complexes ofruthenium, osmium, iron (e.g., polyvinylferrocene or hexacyanoferrate),or cobalt, including metallocene compounds thereof, for example.Suitable ligands for the metal complexes can also include, for example,bidentate or higher denticity ligands such as, for example, bipyridine,biimidazole, phenanthroline, or pyridyl(imidazole). Other suitablebidentate ligands can include, for example, amino acids, oxalic acid,acetylacetone, diaminoalkanes, or o-diaminoarenes. Any combination ofmonodentate, bidentate, tridentate, tetradentate, or higher denticityligands can be present in a metal complex, e.g., osmium complex, toachieve a full coordination sphere.

In certain embodiments, electron transfer agents disclosed herein cancomprise suitable functionality to promote covalent bonding to a polymer(also referred to herein as a polymeric backbone) within the activeareas as discussed further below. For example, but not by way oflimitation, an electron transfer agent for use in the present disclosurecan include a polymer-bound electron transfer agent. Suitablenon-limiting examples of polymer-bound electron transfer agents includethose described in U.S. Pat. Nos. 8,444,834, 8,268,143 and 6,605,201,the disclosures of which are incorporated herein by reference in theirentirety. In certain embodiments, the electron transfer agent is abidentate osmium complex bound to a polymer described herein, e.g., apolymeric backbone described in Section 5 below. In certain embodiments,the polymer-bound electron transfer agent shown in FIG. 3 of U.S. Pat.No. 8,444,834 can be used in a sensor of the present disclosure.

In certain embodiments of the present disclosure, an analyte sensor caninclude at least one NAD(P) depot, at least one permeable layer disposedupon the NAD(P) depot, at least one working electrode, e.g., permeableelectrode, and at least one analyte-responsive active area disposed uponthe surface of the working electrode, where the analyte-responsiveactive area includes at least one NAD(P)-dependent enzyme and at leastone redox mediator, e.g., an osmium complex. In certain embodiments, theanalyte-responsive active area includes an enzyme system comprising adiaphorase, an NAD(P)-dependent dehydrogenase, e.g., β-hydroxybutyratedehydrogenase, and a redox mediator, e.g., an osmium complex.

5. Polymeric Backbone

In certain embodiments, one or more active sites for promoting analytedetection can include a polymer to which an enzyme and/or redox mediatoris covalently bound. Any suitable polymeric backbone can be present inthe active area for facilitating detection of an analyte throughcovalent bonding of the enzyme and/or redox mediator thereto.Non-limiting examples of suitable polymers within the active areainclude polyvinylpyridines, e.g., poly(-vinylpyridine) and/orpoly(-vinylpyridine), and polyvinylimidazoles, e.g.,poly(N-vinylimidazole) and poly(l-vinylimidazole), or a copolymerthereof, for example, in which quaternized pyridine groups serve as apoint of attachment for the redox mediator or enzyme thereto.Illustrative copolymers that can be suitable for inclusion in the activeareas include those containing monomer units such as styrene,acrylamide, methacrylamide, or acrylonitrile, for example. In certainembodiments, polymers that can be present in an active area include apolyurethane or a copolymer thereof, and/or polyvinylpyrrolidone. Incertain embodiments, polymers that can be present in the active areainclude, but are not limited to, those described in U.S. Pat. No.6,605,200, incorporated herein by reference in its entirety, such aspoly(acrylic acid), styrene/maleic anhydride copolymer,methylvinylether/maleic anhydride copolymer (GANTREZ polymer),poly(vinylbenzylchloride), poly(allylamine), polylysine,poly(4-vinylpyridine) quaternized with carboxypentyl groups, andpoly(sodium 4-styrene sulfonate). In certain embodiments where theanalyte sensor includes two active sites, the polymer within each activearea can be the same or different.

In certain embodiments, the polymer is polyvinylpyridine or a copolymerthereof. In certain embodiments, the polymer is a co-polymer ofvinylpyridine and styrene.

In certain embodiments, when an enzyme system with multiple enzymes ispresent in a given active area, all of the multiple enzymes can becovalently bonded to the polymer. In certain other embodiments, only asubset of the multiple enzymes is covalently bonded to the polymer. Forexample, and not by the way of limitation, one or more enzymes within anenzyme system can be covalently bonded to the polymer and at least oneenzyme can be non-covalently associated with the polymer, such that thenon-covalently bonded enzyme is physically retained within the polymer.In certain embodiments, the NAD(P)-dependent enzyme can be covalentlybonded to the polymer. Alternatively, the NAD(P)-dependent enzyme can benon-covalently associated with the polymer. In certain embodiments, theNAD(P)-dependent dehydrogenase and the diaphorase can be covalentlybonded to a polymer within an active area of the disclosed analytesensors. In certain embodiments, the NAD(P)-dependent dehydrogenase canbe covalently bonded to the polymer and diaphorase can be non-covalentlyassociated with the polymer. Alternatively, diaphorase can be covalentlybonded to the polymer and the NAD(P)-dependent dehydrogenase can benon-covalently associated with the polymer.

In certain embodiments, when a stabilizer is present in an active area,one or more enzymes within the area can be covalently bonded to thestabilizer. For example, and not by the way of limitation, one or moreenzymes within an enzyme system, e.g., one or more NAD(P)-dependentenzymes, can be covalently bonded to the stabilizer, e.g., albumin,present in the active area.

In certain particular embodiments, covalent bonding of the one or moreenzymes and/or redox mediators to the polymer and/or stabilizer in agiven active area can take place via crosslinking introduced by asuitable crosslinking agent. In certain embodiments, crosslinking of thepolymer to the one or more enzymes and/or redox mediators can reduce theoccurrence of delamination of the enzyme compositions from an electrode.Suitable crosslinking agents can include one or more crosslinkablefunctionalities such as, but not limited to, vinyl, alkoxy, acetoxy,enoxy, oxime, amino, hydroxyl, cyano, halo, acrylate, epoxide andisocyanato groups. In certain embodiments, the crosslinking agentcomprises one or more, two or more, three or more or four or moreepoxide groups. For example, but not by way of limitation, a crosslinkerfor use in the present disclosure can include mono-, di-, tri- andtetra-ethylene oxides. In certain embodiments, crosslinking agents forreaction with free amino groups in the enzyme (e.g., with the free sidechain amine in lysine) can include crosslinking agents such as, forexample, polyethylene glycol dibutyl ethers, polypropylene glycoldimethyl ethers, polyalkylene glycol allyl methyl ethers, polyethyleneglycol diglycidyl ether (PEGDGE) or other polyepoxides, cyanuricchloride, N-hydroxysuccinimide, imidoesters, epichlorohydrin, orderivatized variants thereof. In certain embodiments, the crosslinkingagent is PEGDGE, e.g., having an average molecular weight (M_(n)) fromabout 200 to 1,000, e.g., about 400. In certain embodiments, thecrosslinking agent is PEGDGE 400. In certain embodiments, thecrosslinking agent can be glutaraldehyde. Suitable crosslinking agentsfor reaction with free carboxylic acid groups in the enzyme can include,for example, carbodiimides. In certain embodiments, the crosslinkingagent is polyethylene glycol diglycidyl ether. In certain embodiments,the crosslinking of the enzyme to the polymer is generallyintermolecular. In certain embodiments, the crosslinking of the enzymeto the polymer is generally intramolecular.

6. Mass Transport Limiting Membrane

In certain embodiments, the analyte sensors disclosed herein furtherinclude a membrane permeable to an analyte that overcoats at least anactive area, e.g., a first active area and/or a second active area.

In certain embodiments, the analyte sensors disclosed herein furtherinclude a membrane permeable to an analyte that overcoats at least oneactive area, e.g., a first active area and/or a second active area. Incertain embodiments, the membrane overcoats each of the active areas ofan analyte sensor. Alternatively, a first membrane overcoats one of theactive areas and a second membrane overcoats the second active area.Alternatively, a first membrane overcoats one of the active areas and asecond membrane overcoats both the first and second active areas.

In certain embodiments, a membrane overcoating an analyte-responsiveactive area can function as a mass transport limiting membrane and/or toimprove biocompatibility. A mass transport limiting membrane can act asa diffusion-limiting barrier to reduce the rate of mass transport of theanalyte, e.g., glucose, an alcohol, a ketone, lactate orO-hydroxybutyrate, when the sensor is in use. For example, but not byway of limitation, limiting access of an analyte, e.g., a ketone, to theanalyte-responsive active area with a mass transport limiting membranecan aid in avoiding sensor overload (saturation), thereby improvingdetection performance and accuracy. In certain embodiments, the masstransport limiting layers limit the flux of an analyte to the electrodein an electrochemical sensor so that the sensor is linearly responsiveover a large range of analyte concentrations.

In certain embodiments, the mass transport limiting membrane can behomogeneous and can be single-component (contain a single membranepolymer). Alternatively, the mass transport limiting membrane can bemulti-component (contain two or more different membrane polymers). Incertain embodiments, the mass transport limiting membrane can includetwo or more layers, e.g., a bilayer or trilayer membrane. In certainembodiments, each layer can comprise a different polymer or the samepolymer at different concentrations or thicknesses. In certainembodiments, the first analyte-responsive active area can be covered bya multi-layered membrane, e.g., a bilayer membrane, and the secondanalyte-responsive active area can be covered by a single membrane. Incertain embodiments, the first analyte-responsive active area can becovered by a multi-layered membrane, e.g., a bilayer membrane, and thesecond analyte-responsive active area can be covered by a multi-layeredmembrane, e.g., a bilayer membrane. In certain embodiments, the firstanalyte-responsive active area can be covered by a single membrane andthe second analyte-responsive active area can be covered by amulti-layered membrane, e.g., a bilayer membrane be covered by a singlemembrane. In certain embodiments, the first analyte-responsive activearea can be covered by a single membrane and the secondanalyte-responsive active area can be covered by a single membrane.

In certain embodiments, a mass transport limiting membrane can includecrosslinked polymers containing heterocyclic nitrogen groups. In certainembodiments, a mass transport limiting membrane can include apolyvinylpyridine-based polymer. Non-limiting examples ofpolyvinylpyridine-based polymers are disclosed in U.S. PatentPublication No. 2003/0042137 (e.g., at Formula 2b), the contents ofwhich are incorporated by reference herein in its entirety.

In certain embodiments, a mass transport limiting membrane can include apolyvinylpyridine (e.g., poly(4-vinylpyridine) orpoly(4-vinylpyridine)), a polyvinylimidazole, a polyvinylpyridinecopolymer (e.g., a copolymer of vinylpyridine and styrene), apolyacrylate, a polyurethane, a polyether urethane, a silicone, apolytetrafluoroethylene, a polyethylene-co-tetrafluoroethylene, apolyolefin, a polyester, a polycarbonate, a biostablepolytetrafluoroethylene, homopolymers, copolymers or terpolymers ofpolyurethanes, a polypropylene, a polyvinylchloride, a polyvinylidenedifluoride, a polybutylene terephthalate, a polymethylmethacrylate, apolyether ether ketone, cellulosic polymers, polysulfones and blockcopolymers thereof including, for example, di-block, tri-block,alternating, random and graft copolymers or a chemically relatedmaterial and the like.

In certain embodiments, a membrane for use in the present disclosure,e.g., a single-component membrane, can include a polyvinylpyridine(e.g., poly(-vinylpyridine) and/or poly(2-vinylpyridine)). In certainembodiments, a membrane for use in the present disclosure, e.g., asingle-component membrane, can include poly(-vinylpyridine). In certainembodiments, a membrane for use in the present disclosure, e.g., asingle-component membrane, can include a copolymer of vinylpyridine andstyrene. In certain embodiments, the membrane can comprise apolyvinylpyridine-co-styrene copolymer. For example, but not by way oflimitation, a polyvinylpyridine-co-styrene copolymer for use in thepresent disclosure can include a polyvinylpyridine-co-styrene copolymerin which a portion of the pyridine nitrogen atoms were functionalizedwith a non-crosslinked polyethylene glycol tail and a portion of thepyridine nitrogen atoms were functionalized with an alkylsulfonic acidgroup. In certain embodiments, a derivatizedpolyvinylpyridine-co-styrene copolymer for use as a membrane polymer canbe the 10Q5 polymer as described in U.S. Pat. No. 8,761,857, thecontents of which are incorporated by reference herein in its entirety.In certain embodiments, the polyvinylpyridine-based polymer has amolecular weight from about 50 Da to about 500 kDa.

In certain embodiments, the membrane can comprise polymers such as, butnot limited to, poly(styrene co-maleic anhydride), dodecylamine andpoly(propylene glycol)-block-polyethylene glycol)-block-poly(propyleneglycol) (2-aminopropyl ether) crosslinked with poly(propyleneglycol)-block-poly(ethylene glycol)-block-poly(propylene glycol)bis(2-aminopropyl ether); poly(N-isopropyl acrylamide); a copolymer ofpoly(ethylene oxide) and poly(propylene oxide); or a combinationthereof.

In certain embodiments, the membrane includes a polyurethane membranethat includes both hydrophilic and hydrophobic regions. In certainembodiments, a hydrophobic polymer component is a polyurethane, apolyurethane urea or poly(ether-urethane-urea). In certain embodiments,a polyurethane is a polymer produced by the condensation reaction of adiisocyanate and a difunctional hydroxyl-containing material. In certainembodiments, a polyurethane urea is a polymer produced by thecondensation reaction of a diisocyanate and a difunctionalamine-containing material. In certain embodiments, diisocyanates for useherein include aliphatic diisocyanates, e.g., containing from about 4 toabout 8 methylene units, or diisocyanates containing cycloaliphaticmoieties. Additional non-limiting examples of polymers that can be usedfor the generation of a membrane of a presently disclose sensor includevinyl polymers, polyethers, polyesters, polyamides, inorganic polymers(e.g., polysiloxanes and polycarbosiloxanes), natural polymers (e.g.,cellulosic and protein based materials) and mixtures (e.g., admixturesor layered structures) or combinations thereof. In certain embodiments,the hydrophilic polymer component is polyethylene oxide and/orpolyethylene glycol. In certain embodiments, the hydrophilic polymercomponent is a polyurethane copolymer. For example, but not by way oflimitation, a hydrophobic-hydrophilic copolymer component for use in thepresent disclosure is a polyurethane polymer that comprises about 10% toabout 50%, e.g., 20%, hydrophilic polyethylene oxide.

In certain embodiments, the membrane includes a siliconepolymer/hydrophobic-hydrophilic polymer blend. In certain embodiments,the hydrophobic-hydrophilic polymer for use in the blend can be anysuitable hydrophobic-hydrophilic polymer such as, but not limited to,polyvinylpyrrolidone, polyhydroxyethyl methacrylate, polyvinylalcohol,polyacrylic acid, polyethers such as polyethylene glycol orpolypropylene oxide, and copolymers thereof, including, for example,di-block, tri-block, alternating, random, comb, star, dendritic andgraft copolymers. In certain embodiments, the hydrophobic-hydrophilicpolymer is a copolymer of poly(ethylene oxide) (PEO) and poly(propyleneoxide) (PPO). Non-limiting examples of PEO and PPO copolymers includePEO-PPO diblock copolymers, PPO-PEO-PPO triblock copolymers, PEO-PPO-PEOtriblock copolymers, alternating block copolymers of PEO-PPO, randomcopolymers of ethylene oxide and propylene oxide and blends thereof. Incertain embodiments, the copolymers can be substituted with hydroxysubstituents.

In certain embodiments, hydrophilic or hydrophobic modifiers can be usedto “fine-tune” the permeability of the resulting membrane to an analyteof interest. In certain embodiments, hydrophilic modifiers such aspoly(ethylene) glycol, hydroxyl or polyhydroxyl modifiers and the like,and any combinations thereof, can be used to enhance thebiocompatibility of the polymer or the resulting membrane.

In certain embodiments where multiple active areas are present, the masstransport limiting membrane can overcoat each active area, including theoption of compositional variation upon differing active areas, which canbe achieved through sequential dip coating operations to produce abilayer membrane portion upon a working electrode located closer to thesensor tip.

In certain embodiments where multiple active areas are present, aseparate mass transport limiting membrane can overcoat each active area.For example, but not by way of limitation, a mass transport limitingmembrane can be disposed on the first active area, e.g., theketones-responsive active area, and a separate, second mass transportlimiting membrane can overcoat the second active area, e.g.,glucose-responsive active area. In certain embodiments, the two masstransport limiting membranes are spatially separated and do not overlapeach other. In certain embodiments, the first mass transport limitingmembrane does not overlap the second mass transport limiting membraneand the second mass transport limiting membrane does not overlap thefirst mass transport limiting membrane. In certain embodiments, thefirst mass transport limiting membrane comprises different polymers thanthe second mass transport limiting membrane. Alternatively, the firstmass transport limiting membrane comprises the same polymers as thesecond mass transport limiting membrane. In certain embodiments, thefirst mass transport limiting membrane comprises the same polymers asthe second mass transport limiting membrane but comprise differentcrosslinking agents.

In certain embodiments, the composition of the mass transport limitingmembrane disposed on an analyte sensor that has two active areas can bethe same or different where the mass transport limiting membraneovercoats each active area. For example, but not by way of limitation,the portion of the mass transport limiting membrane overcoating theketones-responsive active area can be multi-component and/or the portionof the mass transport limiting membrane overcoating theglucose-responsive active area can be single-component. Alternatively,the portion of the mass transport limiting membrane overcoating theketones-responsive active area can be single-component and/or theportion of the mass transport limiting membrane overcoating theglucose-responsive active area can be multi-component.

In certain embodiments, a glucose-responsive active area can beovercoated with a membrane comprising a polyurethane, a polyurethaneurea or poly(ether-urethane-urea). In certain embodiments, aglucose-responsive active area can be overcoated with a membranecomprising a polyurethane. In certain embodiments of the presentdisclosure, the ketones-responsive active area and the secondanalyte-responsive area, e.g., glucose-responsive active area, can beovercoated with a membrane comprising a polyvinylpyridine-co-styrenecopolymer.

In certain embodiments, a membrane, e.g., a single-component membrane,can include a polyvinylpyridine. In certain embodiments, a membrane,e.g., a single-component membrane, can include a copolymer ofvinylpyridine and styrene (or a derivative thereof).

In certain embodiments, the multi-component membrane can be present as abilayer membrane or as a homogeneous admixture of two or more membranepolymers. A homogeneous admixture can be deposited by combining the twoor more membrane polymers in a solution and then depositing the solutionupon a working electrode, e.g., dipping. In certain embodiments of thepresent disclosure, a first analyte-responsive active area, e.g., aketones-responsive active area, can be overcoated with a multi-componentmembrane comprising a polyvinylpyridine and apolyvinylpyridine-co-styrene copolymer, either as a bilayer membrane ora homogeneous admixture, and a second analyte-responsive active area,e.g., a glucose-responsive active area, can be overcoated with amembrane comprising a polyvinylpyridine-co-styrene copolymer.

A suitable copolymer of vinylpyridine and styrene can have a styrenecontent ranging from about 0.01% to about 50% mole percent, or fromabout 0.05% to about 45% mole percent, or from about 0.1% to about 40%mole percent, or from about 0.5% to about 35% mole percent, or fromabout 1% to about 30% mole percent, or from about 2% to about 25% molepercent, or from about 5% to about 20% mole percent. Substitutedstyrenes can be used similarly and in similar amounts. A suitablecopolymer of vinylpyridine and styrene can have a molecular weight of 5kDa or more, or about 10 kDa or more, or about 15 kDa or more, or about20 kDa or more, or about 25 kDa or more, or about 30 kDa or more, orabout 40 kDa or more, or about 50 kDa or more, or about 75 kDa or more,or about 90 kDa or more, or about 100 kDa or more. In non-limitingexamples, a suitable copolymer of vinylpyridine and styrene can have amolecular weight ranging from about 5 kDa to about 150 kDa, or fromabout 10 kDa to about 125 kDa, or from about 15 kDa to about 100 kDa, orfrom about 20 kDa to about 80 kDa, or from about 25 kDa to about 75 kDa,or from about 30 kDa to about 60 kDa.

Polydimethylsiloxane (PDMS) can be incorporated in any of the masstransport limiting membranes disclosed herein.

In certain embodiments, an analyte sensor described herein can comprisea sensor tail comprising at least an NAD(P) depot, a permeable polymerthat overcoats the NAD(P) depot, a first permeable working electrode, afirst active area disposed upon a surface of the first working electrodeand a mass transport limiting membrane permeable to the first analytethat overcoats at least the first active area.

In certain embodiments, the first active area comprises at least oneNAD(P)-dependent-enzyme (optionally, covalently bonded to a firstpolymer present within the active area) that is responsive to a firstanalyte. For example, but not by way of limitation, an analyte sensordescribed herein can comprise a sensor tail comprising at least anNAD(P) depot, a permeable polymer that overcoats the NAD(P) depot, afirst working electrode, an analyte-responsive active area comprising atleast one NAD(P)-dependent-enzyme disposed upon a surface of the firstworking electrode and a mass transport limiting membrane permeable tothe analyte that overcoats the analyte-responsive active area.

In certain embodiments, the first active area comprises a first polymerand an enzyme responsive, e.g., an NAD(P)-dependent enzyme, to a firstanalyte, e.g., glucose, that is, optionally, covalently bonded to afirst polymer. For example, but not by way of limitation, an analytesensor described herein can comprise a sensor tail comprising at leastan NAD(P) depot, a first working electrode, a glucose-responsive activearea comprising a glucose dehydrogenase (optionally, covalently bondedto a first polymer) disposed upon a surface of the first workingelectrode and a mass transport limiting membrane permeable to glucosethat overcoats the glucose-responsive active area.

In certain embodiments, the first active area comprises a first polymerand an enzyme system responsive to a first analyte, e.g., ketones, thatcomprises at least one enzyme, e.g., an NAD-dependent enzyme, that is,optionally, covalently bonded to the first polymer. For example, but notby way of limitation, an analyte sensor described herein can comprise asensor tail comprising at least an NAD(P) depot, a first workingelectrode, a ketones-responsive active area comprising an enzyme systemcomprising β-hydroxybutyrate dehydrogenase and diaphorase (where one orboth enzymes are covalently bonded to a polymer) disposed upon a surfaceof the first working electrode and a mass transport limiting membranepermeable to ketones that overcoats the ketones-responsive active area.

In certain embodiments when a first active area and a second active areaconfigured for assaying different analytes are disposed on separateworking electrodes, the mass transport limiting membrane can havediffering permeability values for the first analyte and the secondanalyte. For example, but not by way of limitation, the mass transportlimiting membrane overcoating at least one of the active areas caninclude an admixture of a first membrane polymer and a second membranepolymer or a bilayer of the first membrane polymer and the secondmembrane polymer. A homogeneous membrane can overcoat the active areanot overcoated with the admixture or the bilayer, wherein thehomogeneous membrane includes only one of the first membrane polymer orthe second membrane polymer. Advantageously, the architectures of theanalyte sensors disclosed herein readily allow a continuous membranehaving a homogenous membrane portion to be disposed upon a first activearea and a multi-component membrane portion to be disposed upon a secondactive area of the analyte sensors, thereby levelizing the permeabilityvalues for each analyte concurrently to afford improved sensitivity anddetection accuracy. Continuous membrane deposition can take placethrough sequential dip coating operations in particular embodiments.

In certain embodiments, when multiple active areas are present, the masstransport limiting membrane can overcoat each active area. In certainembodiments, a mass transport limiting layer is a membrane composed ofcrosslinked polymers containing heterocyclic nitrogen groups, such aspolymers of polyvinylpyridine and polyvinylimidazole. Embodiments alsoinclude membranes that are made of a polyurethane, or polyetherurethane, or chemically related material, or membranes that are made ofsilicone, and the like. In certain embodiments, the mass transportlimiting membrane can include a membrane polymer, such as apolyvinylpyridine or polyvinylimidazole homopolymer or copolymer, whichcan be further crosslinked with a suitable crosslinking agent. Incertain particular embodiments, the membrane polymer can include acopolymer of vinylpyridine and styrene.

In certain embodiments, the mass transport limiting membrane cancomprise a membrane polymer crosslinked with a crosslinking agentdisclosed herein and above in section 5. In certain embodiments wherethere are two mass transport limiting membranes, e.g., a first masstransport limiting membrane and a second mass transport limitingmembrane, each membrane can be crosslinked with a different crosslinkingagent. For example, but not by way of limitation, the crosslinking agentcan result in a membrane that is more restrictive to diffusion ofcertain compounds, e.g., analytes within the membrane, or lessrestrictive to diffusion of certain compounds, e.g., by affecting thesize of the pores within the membrane. For example, but not by way oflimitation, in a sensor that is configured to detect ketones andglucose, the mass transport limiting membrane overcoating theketones-responsive area can have a pore size that restricts thediffusion of compounds larger than ketones, e.g., glucose, through themembrane.

In certain embodiments, crosslinking agents for use in the presentdisclosure can include polyepoxides, carbodiimide, cyanuric chloride,triglycidyl glycerol, N-hydroxysuccinimide, imidoesters, epichlorohydrinor derivatized variants thereof. In certain embodiments, a membranepolymer overcoating one or more active areas can be crosslinked with abranched crosslinker, e.g., which can decrease the amount ofextractables obtainable from the mass transport limiting membrane.Non-limiting examples of a branched crosslinker include branchedglycidyl ether crosslinkers, e.g., including branched glycidyl ethercrosslinkers that include two or three or more crosslinkable groups. Incertain embodiments, the branched crosslinker can include two or morecrosslinkable groups, such as polyethylene glycol diglycidyl ether. Incertain embodiments, the branched crosslinker can include three or morecrosslinkable groups, such as polyethylene glycol tetraglycidyl ether.In certain embodiments, the mass transport limiting membrane can includepolyvinylpyridine or a copolymer of vinylpyridine and styrenecrosslinked with a branched glycidyl ether crosslinker including two orthree crosslinkable groups, such as polyethylene glycol tetraglycidylether or polyethylene glycol diglycidyl ether. In certain embodiments,the epoxide groups of a polyepoxides, e.g., polyethylene glycoltetraglycidyl ether or polyethylene glycol diglycidyl ether, can form acovalent bond with pyridine or an imidazole via epoxide ring openingresulting in a hydroxyalkyl group bridging a body of the crosslinker tothe heterocycle of the membrane polymer.

In certain embodiments, the crosslinking agent is polyethylene glycoldiglycidyl ether (PEGDGE). In certain embodiments, the PEGDGE used topromote crosslinking (e.g., intermolecular crosslinking) between two ormore membrane polymer backbones can exhibit a broad range of suitablemolecular weights. In certain embodiments, the molecular weight of thePEGDGE can range from about 100 g/mol to about 5,000 g/mol. The numberof ethylene glycol repeat units in each arm of the PEGDGE can be thesame or different, and can typically vary over a range within a givensample to afford an average molecular weight. In certain embodiments,the PEGDGE for use in the present disclosure has an average molecularweight (M_(n)) from about 200 to 1,000, e.g., about 400. In certainembodiments, the crosslinking agent is PEGDGE 400.

In certain embodiments, the polyethylene glycol tetraglycidyl ether usedto promote crosslinking (e.g., intermolecular crosslinking) between twoor more membrane polymer backbones can exhibit a broad range of suitablemolecular weights. Up to four polymer backbones may crosslinked with asingle molecule of the polyethylene glycol tetraglycidyl ethercrosslinker. In certain embodiments, the molecular weight of thepolyethylene glycol tetraglycidyl ether can range from about 1,000 g/molto about 5,000 g/mol. The number of ethylene glycol repeat units in eacharm of the polyethylene glycol tetraglycidyl ether can be the same ordifferent, and can typically vary over a range within a given sample toafford an average molecular weight. In certain embodiments, the masstransport limiting membrane can be deposited directly onto the activearea.

In certain embodiments, the mass transport limiting membrane has athickness, e.g., dry thickness, ranging from about 0.1 μm to about 1,000μm, e.g., from about 1 μm to about 500 μm, about 10 μm to about 100 μmor about 10 μm to about 100 μm. In certain embodiments, the masstransport limiting membrane can have a thickness from about 0.1 μm toabout 10 μm, e.g., from about 0.5 μm to about 10 μm, from about 1 μm toabout 10 μm, from about 1 μm to about 5 μm or from about 0.1 μm to about5 μm. In certain embodiments, the sensor can be dipped in the masstransport limiting membrane solution more than once. For example, butnot by way of limitation, a sensor (or working electrode) of the presentdisclosure can be dipped in an interference domain solution at leasttwice, at least three times, at least four times or at least five timesto obtain the desired interference domain thickness.

7. Interference Domain

In certain embodiments, the sensor of the present disclosure, e.g.,sensor tail, can further comprise an interference domain. In certainembodiments, the interference domain can include a polymer domain thatrestricts the flow of one or more interferants, e.g., to the surface ofthe working electrode. In certain embodiments, the interference domaincan function as a molecular sieve that allows analytes and othersubstances that are to be measured by the working electrode to passthrough, while preventing passage of other substances such asinterferents. In certain embodiments, the interferents can affect thesignal obtained at the working electrode. Non-limiting examples ofinterferents include acetaminophen, ascorbate, ascorbic acid, bilirubin,cholesterol, creatinine, dopamine, ephedrine, ibuprofen, L-dopa,methyldopa, salicylate, tetracycline, tolazamide, tolbutamide,triglycerides, urea and uric acid.

In certain embodiments, the interference domain is located between theworking electrode and one or more active areas, e.g., ketones-responsiveactive area. In certain embodiments, non-limiting examples of polymersthat can be used in the interference domain include polyurethanes,polymers having pendant ionic groups and polymers having controlled poresize. In certain embodiments, the interference domain is formed from oneor more cellulosic derivatives. Non-limiting examples of cellulosicderivatives include polymers such as cellulose acetate, celluloseacetate butyrate, 2-hydroxyethyl cellulose, cellulose acetate phthalate,cellulose acetate propionate, cellulose acetate trimellitate and thelike.

In certain embodiments, the interference domain is part of the masstransport limiting membrane and not a separate membrane.

In certain embodiments, the interference domain includes a thin,hydrophobic membrane that is non-swellable and restricts diffusion ofhigh molecular weight species. For example, but not by way oflimitation, the interference domain can be permeable to relatively lowmolecular weight substances, such as hydrogen peroxide, whilerestricting the passage of higher molecular weight substances, such asketones, glucose, acetaminophen and/or ascorbic acid.

In certain embodiments, the interference domain can be depositeddirectly onto the working electrode, e.g., onto the surface of thepermeable working electrode. In certain embodiments, the interferencedomain has a thickness, e.g., dry thickness, ranging from about 0.1 μmto about 1,000 μm, e.g., from about 1 μm to about 500 μm, about 10 μm toabout 100 μm or about 10 μm to about 100 μm. In certain embodiments, theinterference domain can have a thickness from about 0.1 μm to about 10μm, e.g., from about 0.5 μm to about 10 μm, from about 1 μm to about 10μm, from about 1 μm to about 5 μm or from about 0.1 μm to about 5 μm. Incertain embodiments, the sensor can be dipped in the interference domainsolution more than once. For example, but not by way of limitation, asensor (or working electrode) of the present disclosure can be dipped inan interference domain solution at least twice, at least three times, atleast four times or at least five times to obtain the desiredinterference domain thickness.

8. Manufacturing

The present disclosure further provides methods for manufacturing thepresently disclosed analyte sensors that includes one or more activeareas, one or more NAD(P) depots and one or more working electrodes.

In certain embodiments, the method includes depositing a compositioncontaining NAD(P) on a substrate to generate an NAD(P) depot. Forexample, but not by way of limitation, the composition can be NAD and/orNADP, which depends on the enzyme present in the active area. In certainembodiments, the method can further include adding a permeable layer ontop of the NAD(P) depot. In certain embodiments, the permeable layer caninclude a polymer that controls the release of the NAD(P) from thedepot. Alternatively, a composition comprising a polymer and NAD(P) canbe deposited onto a substrate to generate an NAD(P) depot. In certainembodiments, the polymer of the NAD(P) depot is curable, e.g.,UV-curable.

In certain embodiments, the method can further include producing apermeable working electrode, e.g., a carbon nanotube electrode, on thepermeable layer.

In certain embodiments, the method can further include depositing anenzyme composition comprising one or more NAD(P)-dependent enzymes,e.g., an NAD(P)-dependent dehydrogenase, on the working electrode. Incertain embodiments, the enzyme composition can include one or moreadditional enzymes, e.g., diaphorase, a crosslinking agent, e.g.,polyethylene glycol diglycidyl ether, a polymer and/or a redox mediator.In certain embodiments, the enzyme composition can be deposited onto thesurface of a working electrode as one large application which covers thedesired portion of the working electrode or in the form of an array of aplurality of enzyme compositions, e.g., spaced apart from each other, togenerate one or more active areas for detecting one or more analytes. Incertain embodiments, the method can further include curing the enzymecomposition.

In certain embodiments, NAD(P), the permeable polymer, the permeableworking electrode and enzyme composition can be prepared as solutionsthat dry or cure to solidify after deposition. Therefore, in certainembodiments, all layers can be deposited in an automated fashion usingsmall-volume liquid handling or similar techniques for high-throughputsensor fabrication.

In certain embodiments, the method can further include adding a membranecomposition on top of the cured enzyme composition and/or around theentire sensor. In certain embodiments, the membrane composition caninclude a polymer, e.g., a polyvinylpyridine, and/or a crosslinkingagent, e.g., polyethylene glycol diglycidyl ether. In certainembodiments, the method can include curing the membrane polymercomposition.

Generally, the thickness of the membrane is controlled by theconcentration of the membrane solution, by the number of droplets of themembrane solution applied, by the number of times the sensor is dippedin or sprayed with the membrane solution, by the volume of membranesolution sprayed on the sensor, and the like, and by any combination ofthese factors. In certain embodiments, the membrane described herein canhave a thickness ranging from about 0.1 micrometers (m) to about 1,000μm, e.g., from about 1 μm to and about 500 μm, about 10 μm to about 100μm or about 10 μm to about 100 μm. In certain embodiments, the sensorcan be dipped in the membrane solution more than once. For example, butnot by way of limitation, a sensor (or working electrode) of the presentdisclosure can be dipped in a membrane solution at least twice, at leastthree times, at least four times or at least five times to obtain thedesired membrane thickness.

In certain embodiments, the membrane can overlay one or more activeareas, and in certain embodiments, the active areas can have a thicknessfrom about 0.1 μm to about 10 μm, e.g., from about 0.5 μm to about 10μm, from about 1 μm to about 10 μm, from about 1 μm to about 5 μm orfrom about 0.1 μm to about 5 μm. In certain embodiments, a series ofdroplets can be applied atop of one another to achieve the desiredthickness of the active area and/or membrane, without substantiallyincreasing the diameter of the applied droplets (i.e., maintaining thedesired diameter or range thereof). In certain embodiments, each singledroplet can be applied and then allowed to cool or dry, followed by oneor more additional droplets. For example, but not by way of limitation,at least one droplet, at least two droplets, at least three droplets, atleast four droplets or at least five droplets are added atop of oneanother to achieve the desired thickness of the active area.

III. Analyte Monitoring

The present disclosure further provides methods of using the analytesensors disclosed herein to detect an analyte in vivo. In certainembodiments, the present disclosure provides methods for detecting oneor more analytes, e.g., one analyte or two analytes. For example, butnot by way of limitation, the present disclosure provides methods fordetecting one or more analytes including glucose, ketones, lactate,oxygen, hemoglobin A1C, albumin, alcohol, alkaline phosphatase, alaninetransaminase, aspartate aminotransferase, bilirubin, blood ureanitrogen, calcium, carbon dioxide, chloride, creatinine, hematocrit,lactate, magnesium, oxygen, pH, phosphorus, potassium, sodium, totalprotein and/or uric acid using one or more NAD(P)-dependent enzymes. Incertain embodiments, the analyte can be ketones, alcohol, glucose and/orlactate using one or more NAD(P)-dependent enzymes. For example, but notby way of limitation, the present disclosure provides methods fordetecting one or more ketones. In certain embodiments, the presentdisclosure provides methods for detecting glucose. In certainembodiments, the present disclosure provides methods for detectingcreatinine. In certain embodiments, the present disclosure providesmethods for detecting lactate. In certain embodiments, the presentdisclosure provides methods for detecting alcohol.

In certain embodiments, the present disclosure provides methods formonitoring in vivo levels of an analyte over time with analyte sensorsthat include an NAD(P) depot and one or more NAD(P)-dependent enzymes,e.g., an NAD(P)-dependent dehydrogenase. Generally, monitoring the invivo concentration of an analyte in a fluid of the body of a subjectincludes inserting at least partially under a skin surface an in vivoanalyte sensor as disclosed herein, contacting the monitored fluid(interstitial, blood, dermal, and the like) with the inserted sensor andgenerating a sensor signal at the working electrode. The presence and/orconcentration of the analyte detected by the analyte sensor can bedisplayed, stored, forwarded and/or otherwise processed. A variety ofapproaches can be employed to determine the concentration of analyte(e.g., glucose, an alcohol, a ketone and/or lactate) with the subjectsensors. In certain embodiments, monitoring the concentration of analyteusing the sensor signal can be performed by coulometric, amperometric,voltammetric, potentiometric, or any other convenient electrochemicaldetection technique.

In certain embodiments, a method for detecting an analyte includes: (i)providing an analyte sensor including: (a) an internal supply of NAD(P);(b) a permeable polymer that overcoats the internal supply of NAD(P);(c) at least a first working electrode that is disposed upon a surfaceof the permeable polymer, wherein the first working electrode is apermeable working electrode; (d) an analyte-responsive active areadisposed upon a surface of the first working electrode, wherein theanalyte-responsive active area comprises an NAD(P)-dependent enzyme; and(e) a mass transport limiting membrane permeable to the analyte thatovercoats at least the analyte-responsive active area; (ii) applying apotential to the first working electrode; (iii) obtaining a first signalat or above an oxidation-reduction potential of the analyte-responsiveactive area, the first signal being proportional to a concentration ofanalyte in a fluid contacting the analyte-responsive active area; and(iv) correlating the first signal to the concentration of analyte in thefluid.

In certain embodiments, a method for detecting one or more ketonesincludes: (i) providing an analyte sensor including: (a) an internalsupply of NAD(P); (b) a permeable polymer that overcoats the internalsupply of NAD(P); (c) at least a first working electrode that isdisposed upon a surface of the permeable polymer, wherein the firstworking electrode is a permeable working electrode; (d) aketone-responsive active area disposed upon a surface of the firstworking electrode, wherein the analyte-responsive active area comprisesβ-hydroxybutyrate dehydrogenase and diaphorase; and (e) a mass transportlimiting membrane permeable to ketones that overcoats at least theanalyte-responsive area; (ii) applying a potential to the first workingelectrode; (iii) obtaining a first signal at or above anoxidation-reduction potential of the ketones-responsive active area, thefirst signal being proportional to a concentration of analyte in a fluidcontacting the analyte-responsive active area; and (iv) correlating thefirst signal to the concentration of ketones in the fluid.

In certain embodiments, the method of the present disclosure can furtherinclude detecting a second analyte by providing an analyte sensor thatincludes a second active area and/or exposing an analyte sensor thatincludes a second active area to a fluid comprising the first analyteand the second analyte. In certain embodiments, the analyte sensor foruse in a method for detecting a first analyte and a second analyte canfurther include a second working electrode; and a second active areadisposed upon a surface of the second working electrode and responsiveto a second analyte differing from the first analyte, where the secondactive area comprises a second polymer, at least one enzyme responsiveto the second analyte covalently bonded to the second polymer and,optionally, a redox mediator covalently bonded to the second polymer;wherein a portion, e.g., second portion, of the mass transport limitingmembrane overcoats the second active area. Alternatively, the secondactive site can be covered by a second mass transport limiting membranethat is separate and/or different than the mass transport limitingmembrane that overcoats the ketones-responsive active area. In certainembodiments, at least one enzyme responsive to the second analytecomprises an enzyme system comprising multiple enzymes that arecollectively responsive to the second analyte.

In certain embodiments, the method further includes attaching anelectronics unit to the skin of the patient, coupling conductivecontacts of the electronics unit to contacts of the sensor, collectingdata using the electronics unit regarding a level of analyte fromsignals generated by the sensor, and forwarding the collected data fromelectronics unit to a receiver unit, e.g., by RF. In certainembodiments, the receiver unit is a mobile telephone. In certainembodiments, the mobile telephone includes an application related to themonitored analyte. In certain embodiments, analyte information isforwarded by RFID protocol, such as Bluetooth, and the like.

In certain embodiments, the analyte sensor can be positioned in a userfor automatic analyte sensing, e.g., continuously or periodically. Incertain embodiments, the level of the analyte can be monitored over atime period ranging from seconds to minutes, hours, days, weeks ormonths. In certain embodiments, the methods disclosed herein can be usedto predict future levels of the analyte, based on the obtainedinformation, such as but not limited to current analyte level at timezero, as well as the rate of change of the analyte concentration oramount.

IV. Exemplary Embodiments

A. In certain non-limiting embodiments, the presently disclosed subjectmatter provides for analyte sensors comprising:

(i) an internal supply of NAD(P);

(ii) a permeable polymer that overcoats the internal supply of NAD(P);

(iii) at least a first working electrode that is disposed upon a surfaceof the permeable polymer, wherein the first working electrode is apermeable working electrode;

(iv) an analyte-responsive active area disposed upon a surface of thefirst working electrode, wherein the analyte-responsive active areacomprises an NAD(P)-dependent enzyme; and

(v) a mass transport limiting membrane permeable to the analyte thatovercoats at least the analyte-responsive area.

A1. The analyte sensor of A, wherein the NAD(P)-dependent enzyme is anNAD(P)-dependent dehydrogenase.

A2. The analyte sensor of A or A1, wherein the permeable workingelectrode comprises a carbon nanotube.

A3. The analyte sensor of any one of A-A2, wherein the permeable polymercomprises poly(propylene glycol) methacrylate and 2-hydroxyethylmethacrylate.

A4. The analyte sensor of any one of A-A3, wherein the analyte isselected from the group consisting of glucose, a ketone, an alcohol,creatinine, lactate and a combination thereof.

A5. The analyte sensor of A4, wherein the analyte is glucose.

A6. The analyte sensor of A4, wherein the analyte is lactate.

A7. The analyte sensor of A4, wherein the analyte is an alcohol.

A8. The analyte sensor of A4, wherein the analyte is a ketone.

A9. The analyte sensor of A5, wherein the NAD(P)-dependent enzyme is aglucose dehydrogenase.

A10. The analyte sensor of A6, wherein the NAD(P)-dependent enzyme is alactate dehydrogenase.

A11. The analyte sensor of A7, wherein the NAD(P)-dependent enzyme is analcohol dehydrogenase.

A12. The analyte sensor of A8, wherein the NAD(P)-dependent enzyme isβ-hydroxybutyrate dehydrogenase.

A13. The analyte sensor of any one of A-A12, wherein theanalyte-responsive active area further comprises diaphorase.

A14. The analyte sensor of any one of A-A13, wherein theanalyte-responsive active area further comprises a redox mediator.

A15. The analyte sensor of any one of A-A14, wherein theanalyte-responsive active area further comprises a stabilizer.

A16. The analyte sensor of A15, wherein the stabilizer comprises analbumin.

A17. The analyte sensor of any one of A-A16, wherein theanalyte-responsive active area further comprises a crosslinking agent.

A18. The analyte sensor of any one of A-A17, wherein the internal supplyof NAD(P) comprises from about 1 μg to about 1,000 μg of NAD(P).

A19. The analyte sensor of any one of A-A18, wherein the mass transportlimiting membrane comprises a polyvinylpyridine (e.g.,poly(4-vinylpyridine) or poly(4-vinylpyridine)), a polyvinylimidazole, apolyvinylpyridine copolymer (e.g., a copolymer of vinylpyridine andstyrene), a polyacrylate, a polyurethane, a polyether urethane, asilicone or a combination thereof.

A20. The analyte sensor of any one of A-A19, further comprising:

(vi) a second working electrode; and

(vii) a second active area disposed upon a surface of the second workingelectrode and responsive to a second analyte differing from the firstanalyte, wherein the second active area comprising at least one enzymeresponsive to the second analyte;

wherein a second portion of the mass transport limiting membraneovercoats the second active area.

B. In certain non-limiting embodiments, the presently disclosed subjectmatter provides a method for detecting an analyte comprising:

(i) providing an analyte sensor comprising:

-   -   (a) an internal supply of NAD(P);    -   (b) a permeable polymer that overcoats the internal supply of        NAD(P);    -   (c) at least a first working electrode that is disposed upon a        surface of the permeable polymer, wherein the first working        electrode is a permeable working electrode;    -   (d) an analyte-responsive active area disposed upon a surface of        the first working electrode, wherein the analyte-responsive        active area comprises an NAD(P)-dependent enzyme; and    -   (e) a mass transport limiting membrane permeable to the analyte        that overcoats at least the analyte-responsive area.

(ii) applying a potential to the first working electrode;

(iii) obtaining a first signal at or above an oxidation-reductionpotential of the first active area, the first signal being proportionalto a concentration of a first analyte in a fluid contacting the firstactive area; and

(iv) correlating the first signal to the concentration of the firstanalyte in the fluid.

B1. The method of B, wherein the NAD(P)-dependent enzyme is anNAD(P)-dependent dehydrogenase.

B2. The method of claim B or B1, wherein the permeable working electrodecomprises a carbon nanotube.

B3. The method of any one of B-B2, wherein the permeable polymercomprises poly(propylene glycol) methacrylate and 2-hydroxyethylmethacrylate.

B4. The method of any one of B-B3, wherein the analyte is selected fromthe group consisting of glucose, a ketone, an alcohol, lactate and acombination thereof.

B5. The method of B4, wherein the analyte is glucose.

B6. The method of B4, wherein the analyte is lactate.

B7. The method of B4, wherein the analyte is an alcohol.

B8. The method of B4, wherein the analyte is a ketone.

B9. The method of B5, wherein the NAD(P)-dependent enzyme is a glucosedehydrogenase.

B10. The method of B6, wherein the NAD(P)-dependent enzyme is a lactatedehydrogenase.

B11. The method of B7, wherein the NAD(P)-dependent enzyme is an alcoholdehydrogenase.

B12. The method of B8, wherein the NAD(P)-dependent enzyme isβ-hydroxybutyrate dehydrogenase.

B13. The method of any one of B-B12, wherein the analyte-responsiveactive area further comprises diaphorase.

B14. The method of any one of B-B13, wherein the analyte-responsiveactive area further comprises a redox mediator.

B15. The method of any one of B-B14, wherein the analyte-responsiveactive area further comprises a stabilizer.

B16. The method of B15, wherein the stabilizer comprises an albumin.

B17. The method of any one of B-B16, wherein the analyte-responsiveactive area further comprises a crosslinking agent.

B18. The method of any one of B-B17, wherein the internal supply ofNAD(P) comprises from about 1 μg to about 1,000 μg of NAD(P).

B19. The method of any one of B-B18, wherein the mass transport limitingmembrane comprises a polyvinylpyridine (e.g., poly(4-vinylpyridine) orpoly(4-vinylpyridine)), a polyvinylimidazole, a polyvinylpyridinecopolymer (e.g., a copolymer of vinylpyridine and styrene), apolyacrylate, a polyurethane, a polyether urethane, a silicone or acombination thereof.

B20. The method of any one of B-B14, wherein the analyte sensor furthercomprises:

-   -   (f) a second working electrode; and    -   (g) a second active area disposed upon a surface of the second        working electrode and responsive to a second analyte differing        from the first analyte, wherein the second active area        comprising at least one enzyme responsive to the second analyte;    -   wherein a second portion of the mass transport limiting membrane        overcoats the second active area.

EXAMPLES

The presently disclosed subject matter will be better understood byreference to the following Example, which is provided as exemplary ofthe presently disclosed subject matter, and not by way of limitation.

Example 1: Preparation of Polymer-Controlled NAD Release System

The present Example provides a method for making a sensor with an NADdepot, as illustrated in FIG. 23A.

The analyte sensor was prepared by depositing various solutions. An NADsolution was first deposited on a thin plastic substrate (support layer)and allowed to dry, leaving solid NAD. Subsequently, a polymer solutioncomposed of a mixture of poly(propylene glycol) methacrylate (POMA) and2-hydroxyethyl methacrylate (HEMA) was deposited on the solid NAD andpolymerized by UV exposure. A carbon nanotube solution was thendeposited and allowed to dry, forming the permeable electrode. Aketone-sensing enzyme composition that includes an enzyme systemcomprising diaphorase and β-hydroxybutyrate dehydrogenase was thendeposited onto the permeable electrode. Finally, the electrodes weresingulated and dip-coated in a membrane solution comprising apolyvinylpyridine and polystyrene copolymer and a crosslinker to formthe outer membrane. A control sensor was made similarly, except no NADwas deposited on the thin plastic substrate (FIG. 23B).

The response of the sensor and the control were then evaluated with 2 mMof β-hydroxybutyrate, which is used as a substitute for ketones presentin vivo. As shown in FIG. 24, control sensors without an NAD depotshowed reduced signal over time as NAD diffused out from the sensinglayer. However, sensors with an NAD depot did not show reduced signalover time as a result of sustained release of NAD from the depot tomaintain a sufficient NAD concentration in the sensing layer. Withoutbeing bound to a theory, it is believed that the outer membrane of thesensor can allow NAD to leach out from the sensing layer, resulting indecreased ketone response over time because NAD is required tofacilitate the flow of electrons from the analyte to the electrode. Asshown in this Example, the use of an NAD depot can overcome suchlimitations by allowing sustained release of NAD from the depot tomaintain a sufficient NAD concentration to be used by the NAD-dependentenzyme in the sensing layer.

Although the presently disclosed subject matter and its advantages havebeen described in detail, it should be understood that various changes,substitutions and alterations can be made herein without departing fromthe spirit and scope of the disclosed subject matter. Moreover, thescope of the present application is not intended to be limited to theparticular embodiments of the process, machine, manufacture, andcomposition of matter, methods and processes described in thespecification. As one of ordinary skill in the art will readilyappreciate from the disclosed subject matter of the presently disclosedsubject matter, processes, machines, manufacture, compositions ofmatter, methods, or steps, presently existing or later to be developedthat perform substantially the same function or achieve substantiallythe same result as the corresponding embodiments described herein can beutilized according to the presently disclosed subject matter.Accordingly, the appended claims are intended to include within theirscope such processes, machines, manufacture, compositions of matter,methods, or steps.

Various patents, patent applications, publications, productdescriptions, protocols, and sequence accession numbers are citedthroughout this application, the inventions of which are incorporatedherein by reference in their entireties for all purposes.

What is claimed is:
 1. An analyte sensor comprising: (i) an internalsupply of NAD(P); (ii) a permeable polymer that overcoats the internalsupply of NAD(P); (iii) at least a first working electrode that isdisposed upon a surface of the permeable polymer, wherein the firstworking electrode is a permeable working electrode; (iv) ananalyte-responsive active area disposed upon a surface of the firstworking electrode, wherein the analyte-responsive active area comprisesan NAD(P)-dependent enzyme; and (v) a mass transport limiting membranepermeable to the analyte that overcoats at least the analyte-responsivearea.
 2. The analyte sensor of claim 1, wherein the NAD(P)-dependentenzyme is an NAD(P)-dependent dehydrogenase.
 3. The analyte sensor ofclaim 1, wherein the permeable working electrode comprises a carbonnanotube.
 4. The analyte sensor of claim 1, wherein the permeablepolymer comprises a polyether-based polymer.
 5. The analyte sensor ofclaim 1, wherein the analyte is selected from the group consisting ofglucose, a ketone, an alcohol, lactate and a combination thereof.
 6. Theanalyte sensor of claim 5, wherein the NAD(P)-dependent enzyme is aglucose dehydrogenase, a lactate dehydrogenase, an alcohol dehydrogenaseor a β-hydroxybutyrate dehydrogenase.
 7. The analyte sensor of claim 6,wherein the analyte-responsive active area further comprises diaphorase.8. The analyte sensor of claim 1, wherein the analyte-responsive activearea further comprises a redox mediator.
 9. The analyte sensor of claim1, further comprising: (vi) a second working electrode; and (vii) asecond active area disposed upon a surface of the second workingelectrode and responsive to a second analyte differing from the firstanalyte, wherein the second active area comprising at least one enzymeresponsive to the second analyte; wherein a second portion of the masstransport limiting membrane overcoats the second active area.
 10. Amethod comprising: (i) providing an analyte sensor comprising: (a) aninternal supply of NAD(P); (b) a permeable polymer that overcoats theinternal supply of NAD(P); (c) at least a first working electrode thatis disposed upon a surface of the permeable polymer, wherein the firstworking electrode is a permeable working electrode; (d) ananalyte-responsive active area disposed upon a surface of the firstworking electrode, wherein the analyte-responsive active area comprisesan NAD(P)-dependent enzyme; and (e) a mass transport limiting membranepermeable to the analyte that overcoats at least the analyte-responsivearea. (ii) applying a potential to the first working electrode; (iii)obtaining a first signal at or above an oxidation-reduction potential ofthe first active area, the first signal being proportional to aconcentration of a first analyte in a fluid contacting the first activearea; and (iv) correlating the first signal to the concentration of thefirst analyte in the fluid.
 11. The method of claim 10, wherein theNAD(P)-dependent enzyme is an NAD(P)-dependent dehydrogenase.
 12. Themethod of claim 10, wherein the permeable working electrode comprises acarbon nanotube.
 13. The method of claim 10, wherein the permeablepolymer comprises a polyether-based polymer.
 14. The method of claim 10,wherein the analyte is selected from the group consisting of glucose, aketone, an alcohol, lactate and a combination thereof.
 15. The method ofclaim 14, wherein the NAD(P)-dependent enzyme is a glucosedehydrogenase, a lactate dehydrogenase, an alcohol dehydrogenase or aβ-hydroxybutyrate dehydrogenase.
 16. The method of claim 15, wherein theanalyte-responsive active area further comprises diaphorase.
 17. Themethod of claim 10, wherein the analyte-responsive active area furthercomprises a redox mediator.
 18. The method of claim 10, wherein theanalyte sensor further comprises: (f) a second working electrode; and(g) a second active area disposed upon a surface of the second workingelectrode and responsive to a second analyte differing from the firstanalyte, wherein the second active area comprising at least one enzymeresponsive to the second analyte; wherein a second portion of the masstransport limiting membrane overcoats the second active area.